Atrial pressure regulation with control, sensing, monitoring and therapy delivery

ABSTRACT

The present disclosure relates to improved capabilities for stabilizing and regulating atrial pressure with a shunt in the atrial septum or a stent in the coronary sinus. The disclosure also includes sensing, monitoring, drug therapy and control capabilities to provide improved treatment of patients with heart disease and other cardiac related conditions.

INCORPORATION BY REFERENCE

The present application incorporates by reference the following applications: U.S. application Ser. No. 13/167,502, filed Jun. 23, 2011; U.S. Provisional Application No. 61/449,566, filed Mar. 4, 2011; U.S. application Ser. No. 12/954,468, filed Nov. 24, 2010, now U.S. Pat. No. 8,752,258; U.S. application Ser. No. 12/719,843, filed Mar. 8, 2010, now U.S. Pat. No. 8,157,860; U.S. Provisional Application No. 61/299,559, filed Jan. 29, 2010; U.S. Provisional Application No. 61/240,085, filed Sep. 4, 2009; U.S. application Ser. No. 12/447,617, filed Apr. 28, 2009; International Application No. PCT/AU2007/001704, filed Nov. 7, 2007; and Australian Patent Application No. AU 2006906202, filed Nov. 7, 2006.

FIELD OF THE INVENTION

The invention relates systems that enabling sensing, monitoring, and delivery of therapy in or to the cardio-pulmonary system. Specifically, in embodiments, the invention provides such capabilities with the use of a device implanted in the atrial septum.

BACKGROUND

Heart failure is a common and potentially lethal condition affecting humans, with sub-optimal clinical outcomes, often resulting in symptoms, morbidity and/or mortality, despite maximal medical treatment. In particular, “diastolic heart failure” refers to the clinical syndrome of heart failure occurring in the context of preserved left ventricular systolic function (ejection fraction) and in the absence of major valvular disease. This condition is characterized by a stiff left ventricle with decreased compliance and impaired relaxation, which leads to increased end-diastolic pressure. Approximately one third of patients with heart failure have diastolic heart failure and there are very few, if any, proven effective treatments.

Symptoms of diastolic heart failure are due, at least in a large part, to an elevation in pressure in the left atrium. In addition to diastolic heart failure, a number of other medical conditions, including systolic dysfunction of the left ventricle and valve disease, can lead to elevated pressures in the left atrium. Increased left atrial pressure often causes acute or chronic breathlessness amongst other problems. In addition, a variety of heart conditions can lead to “right heart failure”, which can result in enlargement of the liver (hepatomegaly), fluid accumulation in the abdomen (ascites) and/or swelling of the lower limbs.

Frequently, patients with diastolic heart failure experience breathlessness due, in part, to elevated pulmonary venous pressure. These patients often feel worse when supine than when sitting or standing, implying that small changes in pulmonary venous pressure have a pronounced effect on symptoms.

In the past, strategies have been described for the relief of high pressure in the right atrium, such as the creation of hole(s) in the native or surgically created septum between the left and right atria. These have been designed for the rare conditions of pulmonary hypertension or cavopulmonary connections for certain complex congenital heart diseases.

The functioning of the heart and the opening and closing of heart valves occur primarily as a result of pressure differences. For example, the opening and closing of the mitral valve between the left atrium and the left ventricle occurs as a result of the pressure differences between the left atrium and the left ventricle. During ventricular diastole (ventricular filling), when ventricles are relaxed, the venous return of blood from the pulmonary veins into the left atrium causes the pressure in the atrium to exceed that in the ventricle. As a result, the mitral valve opens, allowing blood to enter the ventricle. As the ventricle contracts during ventricular systole (ventricular emptying), the intraventricular pressure rises above the pressure in the atrium and pushes the mitral valve shut. Blood then is pumped from the ventricles to the arteries.

The heart has four valves to ensure that blood does not flow in the wrong direction during the cardiac cycle; that is, to ensure that the blood does not back flow from the ventricles into the corresponding atria, or back flow from the arteries into the corresponding ventricles. The valve between the left atrium and the left ventricle is the mitral valve. The valve between the right atrium and the right ventricle is the tricuspid valve. The pulmonary valve is at the opening of the pulmonary artery. The aortic valve is at the opening of the aorta.

Blood flowing back from the left ventricle into the left atrium, or systolic dysfunction of the left ventricle and valve disease, as mentioned in the background, may cause high atrial pressure and reduce the flow of blood into the left atrium from the lungs. As blood backs up into the pulmonary system, fluid leaks into the lungs and causes pulmonary edema. Blood volume going to the atrium reduces volume of blood going forward into the aorta causing low cardiac output. Excess blood in the atrium over-fills the ventricle during each cardiac cycle and causes volume overload in the left ventricle.

Heart failure with such symptoms is a common and potentially lethal condition affecting humans, with sub-optimal clinical outcomes often resulting in symptoms, morbidity and/or mortality, despite maximal medical treatment. In particular, “diastolic heart failure” refers to the clinical syndrome of heart failure occurring in the context of preserved left ventricular systolic function (ejection fraction) and in the absence of major valvular disease. This condition is characterized by a stiff left ventricle with decreased compliance and impaired relaxation, which leads to increased end-diastolic pressure. Approximately one third of patients with heart failure have diastolic heart failure and there are very few, if any, proven effective treatments.

Symptoms of diastolic heart failure are due, at least in a large part, to an elevation in pressure in the left atrium. In addition to diastolic heart failure, a number of other medical conditions, including systolic dysfunction of the left ventricle and valve disease, can lead to elevated pressures in the left atrium. Increased left atrial pressure often causes acute or chronic breathlessness amongst other problems. In addition, a variety of heart conditions can lead to “right heart failure”, which can result in enlargement of the liver (hepatomegaly), fluid accumulation in the abdomen (ascites) and/or swelling of the lower limbs.

Frequently, patients with diastolic heart failure experience breathlessness due, in part, to elevated pulmonary venous pressure. These patients often feel worse when supine than when sitting or standing, implying that small changes in pulmonary venous pressure have a pronounced effect on symptoms.

In the past, strategies have been described for the relief of high pressure in the right atrium, such as the creation of hole(s) in the native or surgically created septum between the left and right atria. These have been designed for the rare conditions of pulmonary hypertension or cavopulmonary connections for certain complex congenital heart diseases. Accordingly, there still exists a need for devices and methods to treat heart failure, particularly diastolic and/or systolic failure of the left ventricle and its consequences.

BRIEF SUMMARY

Embodiments include an implantable device, which can be referred to herein as a venting device, a stent, flow control device, a prosthesis, an atrial or intra-atrial pressure vent, intercardiac pressure vents/devices, atrial or intra-atrial pressure regulating device, implantable device. The above terms and synonyms of such terms will be used herein interchangeably and shall have the same meaning unless an alternate meaning is made explicitly clear. In some embodiments, the implantable device may comprise may comprise a body assembly. In embodiments, the body assembly refers to the primary structural portion of the device which may comprise, or otherwise itself be, what is referred to herein as a core segment. In embodiments, optionally a flow control element is included. Not all embodiments comprise a flow control element or the like, and those skilled in the art will appreciate that even embodiments described in connection with a flow control element, need not necessarily contain a flow control element or the like. To that end, the designs, methods, configurations of components, etc. disclosed herein have been described along with various configurations. For example, embodiments may be described which include flow control elements or features of the implantable device; however, those skilled in the art will appreciate where the designs, components, configurations or components described herein can be used in combination, or interchangeably, and that the description herein does not limit such interchangeability or combination of components to only that which is described herein.

One embodiment is a system for treating a heart condition in a patient. The device includes a body element including i. a cylindrical core segment defining a passage, ii. a first annular flange adapted to engage a first surface of an atrial septum of the patient, and iii. a second annular flange adapted to engage a second surface of the atrial septum of the patient. The device also includes a microprocessor mounted to the body element, and a sensor in communication with the microprocessor.

Another embodiment is a device for treating a heart condition in a patient. The device includes a flow control device for mounting on an atrial septum of the patient, means for mounting the device on the atrial septum, wherein the means for mounting includes portions within the left atrium and portions within the right atrium of the patient, a microprocessor mounted to the body flow control device and a sensor mounted within the patient.

Another embodiment is a method for treating a heart condition in a patient. The method includes steps of sensing a heart condition in the patient with a sensor implanted within the patient, transmitting information concerning the heart condition to a microprocessor mounted to a flow control device on an atrial septum of the patient, and administering a medication to the patient from a therapeutic administration facility mounted within the patient.

Another embodiment is a method for treating a heart condition in a patient. The method includes steps of sensing a heart condition in the patient with a sensor implanted within the patient, transmitting information concerning the heart condition to a microprocessor mounted to a flow control device on an atrial septum of the patient, and adjusting a flow of blood through the atrial septum of the patient by manipulating a flow control device responsive to a command from the microprocessor.

Embodiments herein leverage the fact that they are implanted in a highly central and invasive location, i.e., the atrial septum or coronary sinus, from which they can obtain a variety of rich data on a continuous or frequent basis.

Some techniques, systems, and methods for deployment of the interatrial pressure devices are described below and in U.S. patent application Ser. No. 13/167,502, which as described above, is incorporated herein by reference in its entirety.

In embodiments of the implantable device, the body assembly may comprise, or itself be referred to as, a core segment, which may comprise a self expanding mesh. In embodiments the body assembly may be collapsible so as to fit into a placement catheter described herein. In embodiments, the body assembly may be both self-explaining and collapsible.

In embodiments, the body assembly may be constructed from preformed wire braid. The wire braid may be formed from nitinol with a martensite/austenite transition temperature is below 37° C. so it remains in its superelastic, austenitic phase during use. The transition temperature is below about 25+/−5° C. The wire should have a diameter of at least about 0.0035 in. (about 0.09 mm) with about 2 lbs. of breaking strength at 200 ksi tensile. The wire should have a very smooth surface to reduce thrombogenicity or irritation response from the tissue. The surface finish may be 63 μin RA or better. This surface may be obtained either by mechanical polishing, by electropolishing or a combination. In embodiments, the surface may be cleaned with detergents, acids and/or solvents to remove residual oils or contamination and then controllably passivated to insure minimal corrosion.

In embodiments, the body assembly may be formed from grade 1 titanium. In embodiments, the body may be formed of grade 6 titanium. In embodiments, the body may be formed of grade 9 titanium. In embodiments, the body may be formed of 316L stainless steel. In embodiments, the body may be formed of 416L stainless steel. In embodiments, the body may be formed of nitinol or cobalt-chromium-nickel alloy (such as Elgiloy®). In embodiments, the body is formed of platinum iridium. In embodiments, the body may be formed of a cobalt chromium alloy. In embodiments, the body may be formed of MP35N®. In embodiments, the body may be formed of Vitalium™. In embodiments, the body may be formed of Ticonium™. In embodiments, the body may be formed of Stellite®. In embodiments, the body may be formed of tantalum. In embodiments, the body may be formed of platinum. Materials disclosed with reference to the body or any component of the device disclosed herein are not meant to be limiting. The skilled artisan will appreciate that other suitable materials may be used for the body or any other component of the device.

In embodiments, the body assembly may be formed from a length of cylindrical tubing that is precut with slots at specific locations and then formed in a series of processes to produce a shape suited for the purpose of containing a flow control element within the interatrial septum.

As an example, a first process might be to stretch the cylinder to expand its internal diameter to a uniform target dimension. This can be done with a balloon or a standard tubing expander consisting of a segmented sleeve and tapered conical inserts that increase the diameter of the sleeve when the cones are advanced toward the center. In order that the shape of the stretched tubing be preserved, the cylinder should be annealed while held into this stretched shape by heating it beyond 300° to 600° for at least about 20 minutes to allow the internal stresses to be relieved. A second process might be to form one flange end shape using a similar process as the first process but using a tool shape specially designed for the first flange shape. A third process might be to form the second flange end shape using a similar process as the first process but using a tool specially designed for the third flange shape. These shapes must be annealed using a similar process as the first shape, either in separate steps or altogether.

In embodiments, the internal diameter of the finished interatrial pressure vent is larger than about 5 mm to enable adequate venting of the left atrium and minimize damage to blood components from excessive shear stress, but enabling the interatrial pressure vent to stow in a placement catheter of smaller than about 14 F.

In embodiments, the flow control element opening is at least about 50 sq. mm. In embodiments, the flow control element opening is 50 sq. mm.±10 sq. mm. In another embodiment, the cylindrical section is formed with an inside diameter of between 3 and 15 mm.

The internal diameter of the body segment may be a constant dimension along the center, longitudinal axis of the interatrial pressure vent and is long enough to isolate the flow control element from deflection or damage as a result of contact with other structural elements of the heart.

In embodiments, the body segment is formed into a substantially toroidal shape, the inner diameter tapering down and then up again from one side of the implant to the other. In embodiments, the length of the body section may be about 4 mm. In embodiments, the length of the body section may be between about 3 mm and about 40 mm.

Other embodiments and advantages of the disclosure will become more apparent from the following detailed description when taken in conjunction with the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

The present disclosure will become more fully apparent from the following description and appended claims, taken in conjunction with the accompanying figures. Understanding that these figures merely depict exemplary embodiments, they are, therefore, not to be considered limiting. It will be readily appreciated that the components of the present disclosure, as generally described and illustrated in the figures herein, could be arranged and designed in a wide variety of different configurations. Nonetheless, embodiments will be described and explained with additional specificity and detail through the use of the accompanying figures in which:

FIG. 1 is a schematic cross-sectional view of a patient's heart with an interatrial pressure vent in situ;

FIG. 2 is an end view of the interatrial pressure vent of FIG. 1 in situ as seen along line 2-2 of FIG. 1;

FIG. 2A is an end-on close up view of a flange segment of an embodiment;

FIG. 2B is an enlarged side cross-sectional view of an embodiment to illustrate variations in flexibility in a flange;

FIG. 3 is a cross-sectional side view taken along line 3-3 of FIG. 2;

FIG. 4 is perspective view of the interatrial pressure vent by itself;

FIG. 5 is a right side view of implantable device of FIG. 4;

FIG. 6 is a distal end view of the implantable device of FIG. 4;

FIG. 7 is an enlarged fragmentary cross-sectional view taken along line 7-7 of FIG. 6;

FIGS. 7A through 7C are a side elevational views of embodiments of the device in the stowed position;

FIG. 8 is a side elevational view of the interatrial pressure vent of FIG. 1 in a collapsed configuration prior to loading in a placement catheter;

FIG. 9 is a side view of the distal end of a placement catheter in its open position;

FIG. 10 is a side view of the distal end of a placement catheter in its open position and with an interatrial pressure vent in its stowed configuration and in position over the inner shaft of the catheter;

FIG. 11 is a side view of the distal end of a placement catheter in a closed configuration with an interatrial pressure vent in its stowed configuration loaded onto the placement catheter;

FIG. 11A is a side view of another embodiment of a placement catheter with an interatrial pressure vent stowed therein;

FIG. 12 is an exploded perspective view of the proximal and distal ends of a placement catheter;

FIG. 13 is a cutaway view of a heart of a patient and the distal end of a placement catheter in position across the interatrial septum;

FIG. 14 is a schematic cross sectional side view of the proximal and distal end of a placement catheter in a closed position and positioned across the interatrial septum of the heart of a patient;

FIG. 15 is a view similar to FIG. 14 but showing the distal end of the placement catheter in a partially open position and the distal flange segments of the interatrial pressure vent deployed;

FIG. 16 is a view similar to FIG. 15 but showing the distal flange segments of the interatrial pressure vent in position against the wall of the interatrial septum;

FIG. 17 is an enlarged cross-sectional detail view of the distal end of the placement catheter of FIG. 16 but showing the distal flange segments of the interatrial pressure vent being retracted from the interatrial septum as if it were determined to be in an undesirable position by imaging the radiopaque markers and going to be redeployed;

FIG. 18 is a view similar to FIG. 16 but showing further deployment of the interatrial pressure vent by releasing the proximal flange segments if imaging determines a correct positioning of the distal flange segments;

FIG. 19 is an enlarged cross-sectional detail view of the placement catheter of FIG. 18 but showing the interatrial pressure vent fully released in position and the placement catheter being removed;

FIG. 19A is schematic depiction of another embodiment of a placement catheter system and interatrial pressure device along with the deployment process therefor;

FIG. 19B is schematic depiction of another embodiment of a placement catheter system and deployment process therefor;

FIG. 20 is a side elevational view of an alternate embodiment of an interatrial pressure vent body with slanted flange segment ends;

FIG. 21 is a side elevational view of an alternate embodiment of an interatrial pressure vent body with staggered flange segment ends;

FIG. 22 is a perspective view of an alternate embodiment of an interatrial pressure vent body with an integrated retrieval means and thrombus clot strain;

FIG. 23 is a right side view of the body assembly of FIG. 22;

FIG. 24 is an end view of an alternate embodiment of interatrial pressure vent;

FIG. 25 is a cross-sectional side view taken along line 25-25 of FIG. 24;

FIG. 26 shows and alternate embodiment wherein the core segment 106 is ovular rather than circular and thus the core segment is a cylindroid or elliptic cylinder rather than a simple cylinder;

FIG. 27 is schematic depiction of another embodiment of a placement catheter system and interatrial pressure device along with the deployment process therefor;

FIG. 27A is a side elevational view of the embodiment described in connection with FIG. 27 in the stowed position;

FIGS. 28A through 28C depict other embodiments of the device that direct the flow of blood in a desired direction;

FIG. 29 is an end-on view from the RA side of embodiments of exit profiles of the flow control element;

FIG. 30 is a side view of an embodiment of the device having a tube-like extension into the RA side of the heart;

FIG. 31 depicts an exploded view of a first embodiment of a mounting and loading tool for mounting and loading a prosthesis;

FIG. 32 depicts an exploded view of a second embodiment of a mounting tool for mounting a prosthesis;

FIGS. 33 and 34 depict the mounting tool with a prosthesis mounted;

FIG. 35 depicts an exploded view of a loading tool for loading a prosthesis on a mounting tool onto a delivery device;

FIG. 36 depicts the prosthesis being loaded into a catheter;

FIG. 37 depicts the loaded catheter with protective packaging;

FIGS. 38A and 38B depict an additional embodiment of a control device or handle for deploying the prosthesis;

FIGS. 39A and 39B depict another embodiment of a control device for deploying the prosthesis;

FIG. 40 depicts another embodiment of a control device or handle;

FIG. 41 depicts a retrieval device useful for retrieving a deployed prosthesis;

FIG. 42 depicts the retrieval device of FIG. 41 with a retrieval basket deployed;

FIG. 43 depicts a closer view of the basket of FIG. 42;

FIGS. 44 and 45 depict retrieval devices using dilators; and

FIGS. 46-49 depict additional embodiments of an implantable prosthesis with retrieval and redeployment features.

FIG. 50 depicts anatomy of a human being and a human heart, with particular focus on the pathways and natural lumens of the body;

FIG. 51 depicts a closer view of a heart and how guide wires and catheters may be maneuvered in and around the heart to deploy embodiments;

FIG. 52 depicts a first catheter extending from the superior vena cava to the coronary sinus of the heart;

FIG. 53 depicts an ablative catheter in the coronary sinus for creating an opening into the left atrium of the heart;

FIG. 54 depicts the ablative catheter creating the opening;

FIG. 55 depicts a balloon catheter for expanding the opening;

FIG. 56 depicts an embodiment for an implantable device used for coronary sinus pressure relief, the device being in a non-deployed state;

FIG. 57 depicts the stent of FIG. 56 in a deployed state;

FIG. 58 depicts a first embodiment of a flange for the atrial wall;

FIG. 59 depicts a second embodiment of a flange for the atrial wall;

FIG. 60 depicts another embodiment of a stent suitable for ensuring communication between the right atrium and the coronary sinus;

FIG. 61 depicts details of a stent with a one-way valve; and

FIGS. 62A and 62B depict another embodiment of a stent.

FIG. 63 depicts a block diagram of an intra-atrial shunt configured with a remote sensing and processing facility.

FIG. 64 depicts an example of an intra-atrial valve with a piezo actuator for moving a flap of the valve to open and close the valve.

FIG. 65 depicts a block diagram of the intra-atrial shunt of FIG. 1 with an incorporated sensing and processing facility.

FIG. 66 depicts a top-level block diagram of treatment and sensor disposition options along with various monitor/control facility options.

FIG. 67 depicts a diagram of an intra-atrial shunt with integrated sensor and drug administration facilities.

FIG. 68 depicts a diagram of an intra-atrial shunt adapted to sense biomarkers in blood flowing through the shunt.

FIG. 69 depicts a flowchart for a method of administering a medication to a patient from a source mounted within or on the patient.

FIG. 70 depicts a flowchart for a method of adjusting a flow control element of the flow control device mounted in a patient's atrial septum.

DETAILED DESCRIPTION

Certain specific details are set forth in the following description and Figures to provide an understanding of various embodiments. Those of ordinary skill in the relevant art will understand that they can practice other embodiments without one or more of the details described below. Finally, while various processes are described with reference to steps and sequences in the following disclosure the steps and sequences of steps should not be taken as required to practice all embodiments of the present disclosure.

As used herein, the terms “subject” and “patient” refer to any animal, such as a mammal like livestock, pets, or humans. Specific examples of “subjects” and “patients” include, but are not limited, to individuals requiring medical assistance, and in particular, requiring treatment for symptoms of heart failure.

As used herein, the term “pressure differential” means the difference in pressure between two points or selected spaces; for example between one side of a flow control element and another side of the flow control element.

As used herein, the term “embolic particle” means any solid, semi-solid, or undissolved material that can be carried by the blood and cause disruption to blood flow when impacted in small blood vessels including thrombi.

As used herein, the terms “radially outward” and “radially away” means any direction which is not parallel with the central axis. For example, considering a cylinder, a radial outward member could be a piece of wire or a loop of wire that is attached or otherwise operatively coupled to the cylinder that is oriented at some angle greater than 0 relative to the center longitudinal axis of the cylinder.

As used herein, the term “axial thickness” means the thickness along an axis parallel to the center longitudinal axis of a shape or component.

As used herein, the term “axial direction” means direction parallel to the center longitudinal axis of a shape or component.

As used herein, a “sealable connection” is an area where components and/or objects meet wherein the connection defines provides for an insubstantial leakage of fluid or blood through the subject area.

As used herein, the term “lumen” means a canal, duct, generally tubular space or cavity in the body of a subject, including veins, arteries, blood vessels, capillaries, intestines, and the like.

As used herein, the term “sealably secured” or “sealably connected” means stably interfaced in a manner that is substantially resistant to movement and provides resistance to the flow of fluid through or around the interface.

As used herein, the term “whole multiple” means the product contains no decimal.

The present disclosure provides structures that enable several unique intracardiac and intraluminal valve devices, loaders, controls and placement devices and catheters therefor. In some embodiments directed toward the intra-cardiac setting, these valve devices are intended to allow sufficient flow from the left atrium to the right atrium to relieve elevated left atrial pressure and resulting patient symptoms but also prevent the amount of flow from the right atrium to the left atrium to minimize the potential for thrombi or other embolic material from entering the arterial circulation.

However, it should be appreciated that embodiments are applicable for use in other parts of the anatomy or for other indications. For instance, a device such as that described in this disclosure could be placed between the coronary sinus and the left atrium for the same indication. Also, a pressure vent such as is described in this disclosure could be placed between the azygous vein and the pulmonary vein for the same indication.

Referring now to FIG. 1, one embodiment of an interatrial pressure vent is shown. FIG. 1 depicts the heart of a human subject. “LA” refers to the left atrium, and “RA” refers to the right atrium. The interatrial septum is depicted as 107. The embodiment of the interatrial pressure vent 100 shown includes a body element 101 and flow control element 104, embodiments of which will be described in further detail below. The body element 101 may comprise flanges 102 and 103. In this and other embodiments described herein, flanges 102 and 103 may be annular flanges, which define a gap 2000 into which the septum 107 fits. In embodiments, after insertion, the interatrial pressure vent is securely situated in an opening created in the interatrial septum. Arrow F in FIG. 1 shows the direction of flow. It can be thus seen that a build up of pressure in the LA can be vented, by way of the inventive device, to the RA.

Referring now to FIG. 2, an embodiment of the interatrial pressure vent is illustrated. This embodiment of an interatrial pressure vent 100 includes body element 101 comprising a substantially open mesh and including a substantially cylindrical core segment (shown end on) 106 and substantially annular flanges 102 and 103. Flanges 102 and 103 may be comprised of any number of flange segments (or “flange elements” or “flange members”) 102 a-102 h and 103 a-103 h, that are attached adjacent to the end of the core segment and extend radially outward from longitudinal axis of the core segment and flow control element 104. “Flange segments” may also be referred to as “legs” herein. The flanges 102 and 103 (and thus the segments which comprise them 102 a-h and 103 a-h) in this and all embodiments disclosed herein, may also be integral with the core segment. That is, they need not be necessarily “attached” thereto but may be fabricated from the same material that defines the core segment (including in the manners described above and herein) and thus may be contiguous therewith. The flow control element may be attached to the body element, for example at locations 105. The flange segments in this and any embodiment of any annular flange may be formed of two individual strut elements or also can be formed of a single element. The flange segments may be generally rectangular in cross section, circular in cross section, oval in cross section or some other geometric shape.

In embodiments, the flange segments are designed to be more flexible than the core segment. In such embodiments, the increased flexibility may be achieved in several ways. In embodiments, a dimension of the surface of the strut elements that make up the flange segments is altered relative to the corresponding dimension of the struts (or elements, or members) that make up the core segments. FIG. 2A illustrates such embodiments. FIG. 2A shows an example flange segment 103 a viewed end on. As shown, the end-facing dimension of strut element of 103× has a width D. By decreasing the width D in relation to the width of the outward-facing dimension of the struts that comprise the core segment, an increased flexibility of the flanges in relation to the core segment or other flange members (or portions thereof) can be achieved. FIG. 2B shows an enlarged fragmentary cross-section of an embodiment of the device substantially shown in FIG. 6. The view is taken along line 7-7 of FIG. 6. In this figure, the cross hatched area shows the area of increased flexibility. It can be seen that one area of the flange segment is thus more flexible than another area. In embodiments where the strut elements are circular, then in a similar fashion, the diameter of the strut element could be made to have a diameters less than the diameter of the strut (or similar elements) comprising the mesh-like configuration of the core segment.

In embodiments where the flange element is made from a different section of material and is attached to the core segment, the segment material could be chosen to have a greater flexibility than the core segment (or remaining portion of the flange segment or flange itself as the case may be). The choice of materials based on their flexibility will be apparent to those skilled in the art. In the ways described above, the flange segments can achieve greater flexibility than the core segment (or the remaining portion of the flange segment or the flange itself as the case may be) thereby reducing probability of damage to the tissue of the septum while allowing the core segment to maintain a strong outward force against the septal opening and thus decrease the probability that the device could become dislodged.

In embodiments having an open-mesh configuration for the body element 101, the body element can be formed from a number of materials suitable for use in a patient, such as titanium, nitinol, stainless steel, Elgiloy®, MP35N®, Vitalium™, Mobilium™, Ticonium™, Platinore™, Stellite®, tantalum, platinum, or other resilient material. Alternatively, in such embodiments, the body element 101 can be formed from a polymer such as PTFE, UHMWPE, HDPE, polypropylene, polysulfone, or other biocompatible plastic. The surface finish of the body element may be smooth with no edges or sharp discontinuities. In other embodiments, the surface finish is textured to induce tissue response and tissue in growth for improved stabilization. In embodiments, the open mesh of body element 101 can be fabricated from a resorbable polymer such as polylactic acid, polyglycolic acid, polycaprolactone, a combination of two or more of these or a variety of other resorbable polymers that are well known to those skilled in the art.

In embodiments, the structure of the body element may be uniform and monolithic.

In other embodiments, the body element (mesh or monolithic) may comprise porous materials to encourage tissue ingrowth or to act as a reservoir for containing one or more compounds that will be released over time after implant to address numerous issues associated with the product performance. These compounds can be used to diminish calcification, protein deposition, thrombus formation, or a combination of some or all of these conditions. The compound can also be used to stimulate an irritation response to induce tissue ingrowth. In embodiments, the compound can be an anti-inflammatory agent to discourage tissue proliferation adjacent to the device. Numerous agents are available for all of such uses and are familiar to those who are skilled in the art.

In embodiments, the material that may comprise the body may be multilayered comprising a coating of resorbable polymer or semipermeable polymer that may comprise various compounds that may be released, and in some embodiments in a controlled manner over time, after implant to address numerous issues associated with product performance.

The mesh can be formed from wire that is pre-bent into the desired shape and then bonded together to connect the component elements either by welding them or adhesively bonding them. They could be welded using a resistance welding technique or an arc welding technique, preferably while in an inert gas environment and with cooling control to control the grain structure in and around the weld site. These joints can be conditioned after the welding procedure to reduce grain size using coining or upset forging to optimize fatigue performance.

In other embodiments, the mesh can be formed from a hollow tube that has been slotted using, for example, a machining laser or water drill or other method and then expanded to form the open structure. If a sufficiently elastic and resilient material, such as nitinol, is used, the structure can be preformed into the finished shape and then elastically deformed and stowed during delivery so the shape will be elastically recovered after deployment. The surface of the finished assembly must be carefully prepared to insure is passivated and free of surface imperfections that could be a nidus for thrombus formation.

In embodiments, the flow control element 104 is a tissue valve such as a tricuspid valve, a bicuspid valve or a single flap valve formed from pericardial tissue from a bovine, porcine, ovine or other animal. Any number of cusps may be used. The flow control element is formed using a number of processing steps and auxiliary materials such as are well known in the art.

The flow control element 104 can also be a ball valve, a duckbill valve, a leaflet valve, a flap valve, a disc in cage type valve, a ball in cage type valve or other type of valve formed from a polymer or polymers or a combination of polymers, ceramics and metals such as Dacron (polyester), PTFE (such as Teflon®), polyurethane, PET or other suitable polymer; titanium, stainless steel, nitinol, MP35N®, cobalt-chromium-nickel alloy (such as Elgiloy®), or other suitable metal; zirconia, silicone nitride, or other suitable ceramic. Valves or portions thereof may comprise different stiffness/flexibly properties with respect to other valves or portions thereof in the flow control element.

The flow control element 104 preferably extends to a point along the flange assembly 103 to enable creation of a sealable connection to the septum wall after placement. This is more particularly shown in FIG. 3 where it can be seen that in embodiments, the flow control element extends beyond the length of the core segment and is folded and attached to the core segment so as to create a lip that extends in a direction center of the opening in the vent. When the device is abutted against the septal wall, this lip forms said sealable connection and thus can reduce the likelihood that blood can flow through the septal opening via pathways between the outer surface (septal-facing surface) of the interatrial pressure venting device and the septal opening. The flow control element 104 is attached to the body element 101. This can be accomplished by using a suture material, such as silk, nylon, polypropylene, polyester, polybutylester or other materials such as are well known to those skilled in the art. In embodiments, flow control element 104 can be attached to body element 101 using adhesive bonding agents such as cyanoacrylate, polymethylmethacrylate, or other materials such as are well known to those skilled in the art. In other embodiments, flow control element 104 can be attached to body element 101 via staples, rivets, rings, clamps or other similar methods as are well known to those skilled in the art.

As mentioned above, flow control element can be made of material selected for its flexibility/stiffness. In embodiments where a loose valve is desired that resonates more closely with the cycle of the heart, a however stiffness material may be chosen. In embodiments where it is desired to open the valve when the pressure differential reaches a selected value, the material of the flow control element can be selected and/or processed in a manner to open at the desired differential. The leaflets or sections of the flow control element itself may also comprise areas of variable stiffness, and or may be more flexible or less flexible than other leaflets or components of the flow control element.

FIG. 3 shows an embodiment of the device implanted in the atrial septum of the heart of a patient. As can be seen from the figure, the core segment 106 can be formed contiguously with flanges 102 and 103 and thus flange segments 102 a-102 h and 103 a-103 h respectively. In the embodiment shown, flow control element 104 is contained within the core segment 106 so it does not extend beyond the face of the body element 101, thereby insulating it from contact from other body structures or peripheral tissue. In embodiments, the core segment 106 can be extended to protrude beyond the interatrial septum 107 and the flange assembly 102 and/or 103 on at least one side of the interatrial septum 107 and can be formed with a shape that extends to create a lip in the manner described above. In embodiments, the ends of the flange assemblies 102, 103 are formed to lie at a parallel angle to and against the septal wall along at least a part of its length to increase the area of contact and thereby decrease the stress concentration against the septal wall.

Referring now to FIG. 4, an embodiment of the implantable device is shown. This perspective view implantable device 101 shows how, in embodiments, the ends of flange segments 102 a-102 h, 103 a-103 h are rounded at their distal ends 115 and 116 to reduce stress concentrations against the interatrial septum after placement. This rounded shape can easily be formed as part of the integral shape of the flange segment. In other embodiments, the thickness of the segment in this area may be decreased to decrease the stress further against the interatrial septum, which is similar to embodiments described above. Also similar to embodiments described above, if the segment is round, the diameter can be decreased in order to increase flexibility. Also, as described above a different material of higher flexibility could be used for the end portions of the segments.

While rounded shapes at the ends of the flange segments reduce stress on the septum, other variations on this theme are contemplated. FIGS. 7A through 7C illustrate embodiments where the shape of the end portions of the flange segments has configurations to achieve less stress against the septal wall—among other goals. FIG. 7A is a side elevational view of embodiment of the pressure venting device in its stowed configuration. Core segment 106 of body element 101 is shown and, in this embodiment, is integral with flanges 103 and 102. The individual flange segments are not labeled; however, it is easily seen that flange 103 comprises segments substantial similar to those described above. There is no eyelet or opening at the end of the segment in the embodiment shown. Flange 102 shows an embodiment where the flange segment is not comprised of a triangular or multi-strut arrangement as described above but rather a single-member segment. Any flange may be constructed with single-member segment. An example single member is referred to as 103 s. In this example, at the end of each single-member flange segment (102 s) for example, there is an eyelet. FIG. 7B shows an embodiment similar to that shown in FIG. 7A where the end of the segments 102 s are not eyelets but rather pads. FIG. 7C shows another embodiment where the ends of the segments 102 are paddle shaped. Other smooth-edged shapes could be used, and it should be understood that such shapes and configurations apply to all manner of flange segment ends, not only single-member segments. This would include the ends of flange segments shown and described herein, for example with reference to FIGS. 2 through 7.

FIGS. 7A-C also show embodiments having at least one flange segment being longer than the other flange segments. Again, while represented as single-member flange segments they need not be and as such a configuration with at least one longer segment may apply to any flange-segment configuration disclosed herein. The benefits and purpose of having at least one longer flange segment will be described more fully below.

In embodiments, the outer ends of the flange segments 102 a-102 h, 103 a-103 h are formed with integral marker holes or slots 109 and 110 (shown in FIGS. 3 and 7 for example) in which markers 118 and 119 can be positioned so the device may more easily be visualized using radiographic imaging equipment such as with x-ray, magnetic resonance, ultrasound or other imaging techniques. Markers as disclosed herein may be applied to the ends of any segments, not just those with holes or eyelets therein. A radiopaque marker 118 and 119 can be swaged, riveted, or otherwise placed and secured in the hole and thereby dimensioned to be flush with the end of the segment. Markers may also be simply attached or to end of a segment not having a hole. In all embodiments having markers, flange ends 115 and 116 are more visible when imaged. In other embodiments, the markers 118 and 119 can be bonded with an adhesive agent such as cyanoacrylate or epoxy or a variety of other materials that are available and suitable for implant as are well known. The markers may be proud (as shown for example in FIG. 7) or flush with the end of the flange segment. The radiopaque markers 118 and 119 may be formed of tantalum, tungsten, platinum iridium or gold alloys of these materials or other materials that are known to those skilled in the art. Also markers 118 and 119 comprising cobalt, fluorine or numerous other paramagnetic materials or other echogenic materials that are known to those skilled in the arts can be incorporated together with the radiopaque materials, or in alternating locations of the flange segments to enable both x-ray and echographic imaging of the interatrial pressure vent. Alternatively, the ends of the flange elements 102 a-102 h and 103 a-103 h can be wrapped with a foil made of the same marker materials. In embodiments, the radiopaque material can be laminated to the flange segments and bonded through a welding process or using an adhesive such as cyanoacrylate or numerous other adhesives known to those skilled in the art.

Suture rings 117 can be formed in the body element to locate and fix the attachment site along the body element to the flow control element. The suture rings can be circular holes formed into the structure or they could also be some other shape such as rectangular or triangular and also can be formed as a secondary step, for example by standard machining techniques, using a secondary laser machining step, or with electro-chemical etching. Preferably the connection between a segment and any other segment of the body element are formed with as large a radius as possible to increase resistance to fatigue failure. Also, preferably, all edges of the formed device are rounded to improve biocompatibility and hemocompatibility.

The pattern of suture rings as well as which of the rings are selected during suturing may affect the properties of the flow control element. For example, in embodiments where it is desired to have the flow element loose and flappable, less suture rings may be utilized and, in such embodiments, RA-side end of the flow control element may contain relatively less sutures than the LA side. In other embodiments, it may be desirable to keep the flow control element affixed to the core segment for an increased length of the segment thereby reducing the amount of flow control element material that affecting flow. Still in other embodiments the top or bottom portion the flow element at the RA side may be sutured in such a way so as to allow the top or bottom portion of the flow control element to affect flow more than the other portion respectively. Embodiments discussed below where the flow is “aimed” may utilize suturing patterns effective to enable the desired flow control element configuration.

Returning to the flange segments, in an embodiment, the interatrial pressure vent 100 is comprised of an equal number of flange segments on each side of the interatrial septum. In embodiments, there are eight flange segments on each side of the core segment. In another aspect there are an equal number of suture rings and flange segments on one side of the interatrial pressure vent. In other embodiments, there are seven flange segments on each side of the core segment. In other embodiments, there are six flange segments on each side of the core segment. In other embodiments, there are five flange segments on each side of the core segment. In other embodiments there are four flange segments on each side of the core segment. In other embodiments there are three flanges on each side of the core segment. In other embodiments there are two flanges on each side of the core segment. In other embodiments, there is one flange on each side of the core segment. Still in other embodiments there are more flange segments as compared to flange segments. And in other embodiments, there are more flange segments as compared to flange segments. As can be seen there are a number of variations for the number of flange segments and the skilled artisan will appreciate that any number could be used while not deviating from the scope and spirit of this disclosure.

Referring now to FIG. 5, an embodiment of the implantable device is displayed in side view. The flange segments can be formed to produce a gap G (also referred to as an annular gap) between the ends of flange segments on one side of the body and flange segments on the other side of the body, when the device is in its “native” or un-deployed state. When the device is deployed, it flexes to accommodate the tissue and as such the gap may expand when tissue is positioned therein. In embodiments, this gap is slightly smaller than the thickness of the interatrial septum. In other embodiments, the gap can be larger than the thickness of the interatrial septum. In other embodiments the gap can be zero. In another aspect the gap can be negative: in this case the flange segments on each side of the body can be formed to cross each other in order to exert more pressure between the deployed flange segments and the interatrial septum. Also shown in FIG. 5 are radiopaque markers 118 and 119, which in embodiments are shown to be located adjacent to the end of the flange segments.

Referring now to the embodiment shown in FIG. 6, the flange segments 102 a-102 h are oriented so they are not directly opposed to flange segments 103 a-103 h on the opposite side of the body element so that after placement there is no pinching points thereby reducing the chance for tissue injury. In embodiments, flange segments 102 a-102 h are arranged midway between adjacent ends of flange segments 103 a-103 h. In embodiments the length of flange segments 102 a-102 h are similar to the length of flange segments 103 a-103 h. However, in other embodiments the length of flange segments 102 a-102 h are identical to the length of flange segments 103 a-103 h; the length of flange segments 102 a-102 h are longer than 103 a-103 h; and the length of flange segments 102 a-102 h are shorter than flange segments 103 a-103 h.

Referring now to FIG. 7, in embodiments having radiopaque markers it can be seen that the radiopaque markers 118 and 119 may be placed into the marker holes 109 and 110 (or placed on the ends of flange segments that do not have holes) to locate the ends of the flange segments 102 a-102 h and 103 a-103 h with a non-invasive imaging technique such as with x-ray or echosound during or after the procedure. In embodiments, the markers 118 and 119 can be formed to be flush in an axial direction with the outer surface and the inner surface of the flange segments 102 a-102 h and 103 a-103 h. In another aspect, the markers 118 and 119 can be formed to extend in an axial direction beyond the outer surface of the flange segments 102 a-102 h and 103 a-103 h, away from the interatrial septum. In embodiments, the markers 118 and 119 can be formed to extend in an axial direction beyond the inside of the flange segments 102 a-102 h and 103 a-103 h, toward the interatrial septum. In embodiments, the markers 118 and 119 can be formed to extend in an axial direction beyond the inside and the outside of the flange segments 102 a-102 h and 103 a-103 h. In embodiments, the markers 118 and 119 can be formed to be recessed in an axial direction within the surface of the inside of the flange segments 102 a-102 h and 103 a-103 h. In embodiments, the markers 118 and 119 can be formed to be recessed in an axial direction within the outside of the flange segments 102 a-102 h and 103 a-103 h. In embodiments, the markers 118 and 119 can be formed to be recessed in an axial direction within both the inside and the outside of the flange segments 102 a-102 h and 103 a-103 h. In embodiments, the markers 118 and 119 can be formed to extend in a radial direction within the width of the flange segments 102 a-102 h and 103 a-103 h. In embodiments, the markers 118 and 119 can be formed to extend in a radial direction flush with the width of the flange segments 102 a-102 h and 103 a-103 h.

Referring now to FIG. 8, an interatrial pressure vent 100 is shown in its stowed configuration. In embodiments, the interatrial pressure vent can be collapsed to a substantially cylindrical shape for stowing in a delivery catheter during placement. Flange segments 102 a-102 h and 103 a-103 h can be fabricated to be substantially equal in length. The “stowed position” is not meant to apply only to devices having flange segments of equal length but rather to all embodiments of the venting device disclosed herein. Devices having flange segments of varying length and orientation such as those described herein are also designed to stow in substantially the same manner as shown in FIG. 8. In an embodiment 200 seen in FIG. 20, flange segments 202 a-202 h and 203 a-203 h are formed on a slanted angle so that, when marker elements are secured to the ends of the flange segments, the flange segments can be stowed into a smaller volume. In embodiments 300 seen in FIG. 21, flange segments 302 a-302 h are formed of alternating length to allow stowage into a smaller volume.

Referring now to FIG. 9, an embodiment of the distal end of the placement catheter 111 is shown in its open position. The inner shaft 112 is fabricated with a center lumen 136 of sufficient diameter to contain a guidewire 138 or also for use in injecting contrast or other liquid. Commonly, the lumen would be sized for a guidewire of 0.010″, 0.011″, 0.014″, 0.018″, 0.021″, 0.028″, 0.035″, 0.038″, 0.042″ or 0.045″. This lumen 136 can also be used to measure pressure at the distal end of the catheter using other equipment and techniques that are well known to those skilled in the art. The lumen 136 preferably extends through the entire length of the inner shaft 112. Alternatively, the guidewire lumen 136 can extend for a shorter length in the proximal direction and then through a side hole (not shown) of the inner sheath. A corresponding side hole (not shown) is placed on the outer shaft 113 adjacent to the side hole in the inner shaft 112 to create a pathway between the center lumen 136 of the inner shaft 112 and the outside of the outer shaft 113. In this way it is possible to pass a guidewire from this distal end of the inner lumen 136 through the side hole and exchange the catheter over a guidewire that is less than twice the length of the catheter 111 while securing the guidewire position during exchange.

In embodiments, the inner shaft 112 is configured with a waist section 120 to contain the folded interatrial pressure vent 100 between the gap formed in the space outside of this section of inner shaft 112 and the inside of the outer shaft 113. The inner shaft 112 may be formed to contain at least one circumferential groove 114 at the proximal end of waist section 120 that forms a recess between the inside of the outer shaft 113 and the smallest diameter of the groove that is greater than the gap formed in the space between the waist section 120 and the inside of the outer shaft 113. Radiopaque markers 118 can extend in a radial direction past the outer surface of the flange segments 102 a-102 h and in embodiments, when interatrial pressure vents are folded into their stowed configuration and placed into position over inner shaft 112, radiopaque markers 118 are dimensioned to fit into groove 114. Other similarly dimensioned sections may be used; that is, that which fits into the groove need not necessarily be a radiopaque marker. In embodiments, when interatrial pressure vents are stowed in this manner, the gap between waist section 120 and the inside of outer shaft 113 is not sufficient to allow radiopaque markers 118 beyond the distal end of groove 114 unless the outer sheath 113 is retracted beyond the proximal end of groove 114.

The inner shaft 112 may be formed with a groove 121 on the distal end of the waist section 120 adjacent to the location of the distal end of the interatrial pressure vents are radiopaque markers 119 (or similar dimensioned members) can extend in a radial direction past the outer surface of the flange segments 102 a-102 h and in embodiments, when interatrial pressure vents are folded into its stowed configuration and placed into position over inner shaft 112, radiopaque markers 119 are dimensioned to fit into groove 121. In another aspect, the inner shaft 112 may be formed with a circumferential groove 114 on the proximal end of waist section 120 and a circumferential groove 121 on the distal end of the waist section 120 The inner shaft can be formed of a variety of polymers or metals or combinations of polymers and metals that are suitable for use in a patient. The inner shaft can be fabricated from a single length of PTFE, UHMWPE, FEP, HDPE, LDPE, polypropylene, acetal, Delrin, nylon, Pebax, other thermoplastic rubber, aliphatic or aromatic polyurethane, or a variety of other engineering resins that are well known to those skilled in the art. In embodiments, the inner shaft can be fabricated using multiple layers of two or three of the above-mentioned polymers to combine desirable properties of each. For example, the outer surface could be composed of polyurethane to enable easier bonding of auxiliary components to the inner shaft. The inner layer could be PTFE to convey better lubricity to the inner shaft. In embodiments, the inner shaft and or the outer shaft could be coated on the inner and or outer surface with a coating material that conveys specific properties to the shaft like antithrombogenicity or lubricity. There are numerous available coating materials suitable for these purposes as are well known to those skilled in the art. The inner shaft can be compounded with a radiopacifier to increase the visibility of the inner shaft under fluoroscopy using bismuth salts such as bismuth subcarbonate, bismuth oxychloride, bismuth trioxide, tungsten powder, molybdenum powder or other radiopacifier such as are well known to those skilled in the arts. Similarly, the outer sheath can be fabricated from the same set of materials as the inner sheath, in the same manner and using the same coatings. Embodiments described below in connection with a flange rather than circumferential groove operate in substantially the same manner as described above and herein, except the device does not necessarily have projections that fit into and are retained by the grooves.

Referring now to FIG. 10, a folded representative interatrial pressure vent 100 is shown in its stowed position with the placement catheter 111 shown in its open position. In practice, if the body of the interatrial pressure vent is fabricated of nitinol or other elastic material, when the placement catheter is in its fully open position, the flange segments 102 a-102 h and 103 a-103 h would automatically recover into a shape like that shown in, for example, FIG. 4, hence this Figure is shown to illustrate the position of the interatrial pressure vent 100 relative to the waist section 120 and grooves 114 and 121. When radiopaque markers (or similarly dimensioned members) 118 extend beyond the thickness of the inside of body segment 101 of interatrial pressure vent 100, they form a projection within interatrial pressure vent 100 that can be captured within groove 114 to secure the position of the interatrial pressure vent 100 during placement. During deployment, the outer shaft 113 of placement catheter 111 is retracted a sufficient distance to reveal the distal portion of the interatrial pressure vent 100 allowing the flange segments 103 a-103 h to dilate radially away from the central longitudinal axis of body 101. By capturing the radiopaque 118 markers within the groove 114, the device can be repositioned easily without further deployment, or the device can be completely retracted and removed from the patient without deployment as indicated in FIG. 17.

Referring now to FIG. 11, an interatrial pressure vent 100 is shown completely stowed within the placement catheter 111.

FIG. 11A shows an embodiment of the placement catheter similar in operation to those described herein but operative to engage an interatrial pressure vent by way of a slightly different mechanism than described above in connection with circumferential grooves. This figure shows a schematic depiction of a stowed interatrial vent. Rather than having the grooves as described above, this embodiment of a placement catheter may comprise an inner shaft having a flange or member 3000 (rather than a groove) which has a diameter larger than that of the inner shaft to grip and hold an end of the interatrial vent device as shown. As shown in the figure, the flange and its segments (collectively referred to in the figure as 102) wrap around the ball-shaped flange 3000 and allow the interatrial pressure vent to be moved with the placement device in the manners described herein.

Referring now to FIG. 12, a placement catheter 111 is shown. It should be noted that while the inner shaft is depicted as having grooves in FIG. 12, the inner shaft may comprise the flange 3000 as described above in connection with FIG. 11A. The skilled artisan will appreciate that the operation of the device is substantially similar whether grooves or flanges are utilized. The placement catheter 111 may comprise a first handle component 128 that can be attached to outer shaft 113. The first handle component can be attached to the outer shaft 113 using a variety of adhesive methods such as solvent bonding using a solvent for both the handle and outer shaft material; an organosol consisting of a solvent and polymer in solution that is compatible with both the outer shaft and the first handle component; a polymerizable adhesive, such as polyurethane, cyanoacrylate, epoxy or a variety of other adhesives as are well known to those skilled in the art. The first handle component can be fabricated from a variety of metals such as aluminum, stainless steel, titanium or a number of other metals and alloys as are well known to those skilled in the art. In embodiments, the first handle component 128 is fabricated from a polymer such as polycarbonate, or a variety of engineering resins, such as Lexan®, or others as are well known to those skilled in the art.

The first handle component may comprise hand grip section 124 and tubular shaft section 125. The tubular shaft section 125 can contain keyway 122 that is formed or machined into the shaft section. The keyway is preferably formed with three linear sections; a first linear section 131, a second linear section 132 and a third linear section 133. Each of these sections is formed to traverse along a path primarily parallel with the center axis along the length of the first handle component but each is displaced radially from one another by at least about half of the width of the keyway. The placement catheter 111 also can comprise a second handle component 129 that can be attached to inner sheath 112. The second handle component can be fabricated from the same variety of metals and polymers as the first handle component. The two handles can be fabricated from the same materials or from different materials. The second handle component can be attached to the inner sheath in the same manner and using the same materials as the first handle component attaches to the outer sheath. In embodiments, the second handle component can contain threaded hole126 for containing set screw 127. The set screw can be twisted to capture the inner shaft against the second handle component. The second handle component 129 also can comprise a second hand grip section 134 and second tubular shaft section 130. The second tubular shaft section can contain key 123 that is formed or machined of suitable dimension to adapt to keyway 122 of first handle component 128. When assembled, second handle component 129 can be slideably moved relative to first handle component 128 in a manner controlled by the shape and length of the key way 122. As the second handle 129 is advanced relative to the first handle 128, it can be appreciated that the inner sheath 112 will slide in a distal direction out from the outer sheath 113. It can be appreciated that when the second handle component 129 is assembled, the key 123 is slid into the first linear section 131 and advanced until it hits the edge of the keyway formed between the first linear section 131 and the second linear section 132. In order for the second handle component 129 to advance further, it must be rotated and, once rotated, it can be advanced further but will stop when the key 123 hits the edge of the keyway formed between the second linear section 132 and the third linear section 133. The keyway dimensions are preferably selected with consideration for the combination of lengths of other components in the placement device.

A first position, defined as the position when the key 123 is in contact with the proximal edge formed between the first linear section 131 and the second linear section 132, is preferably determined so, when fully assembled and with the interatrial vent in its stowed position within the placement catheter, the outer shaft 113 will completely cover the length of the interatrial pressure vent 100 as is desired during catheter placement. The keyway dimensions can also be selected to result in a second position, defined as the position when the key 123 is in contact with the distal edge formed between the second linear section 132 and third linear section 133. The second position would preferably be selected to reveal the full length of flange segments 103 a-103 h but retain flange segments 102 a-102 h within the outer shaft 113 of the catheter. The length of the third linear section 133 would preferably be selected so that, when the second handle component 129 was advanced completely against the first handle component 128, the full length of the interatrial vent 100 would be uncovered by the outer shaft 113 and the device would be deployed. A variety of other configurations of the first and second handle components could be used for this same purpose. The first handle component tubular shaft section 125 and the second handle component tubular shaft section 130 could be threaded (not shown) so the first handle component 128 could be screwed into the second handle component 129. Alternatively, gear teeth (not shown) could be formed in the first tubular shaft section 125 of the first handle component 128 and a gear wheel (not shown) could be incorporated into the second shaft tubular section 130 of the second handle component 129. The gear wheel would preferably be chosen to mesh with the gear teeth and the second handle component 129 could be advanced toward the first handle component 128 by rotating the gear wheel. A variety of other design configurations could be utilized to control the relative location between the first handle component and the second handle component as are well known to those skilled in the art.

FIGS. 13 through 17 show embodiments of a system for treating heart failure. More specifically FIGS. 12 through 19 show how the placement catheter is introduced and positioned in a patient and methods for placing the interatrial valve in a patient. The interatrial pressure vent 100 is presterilized and packaged separately from the placement catheter 111. Sterilization can be performed by exposing the device to a sterilizing gas, such as ethylene oxide, by exposing the device to elevated temperature for an adequate period of time, by using ionizing radiation, such as gamma rays or electron beam or by immersing the device in a fluid that chemically crosslinks organic molecules, such as formaldehyde or glutaraldehyde and then rinsed in sterile water or sterile saline. For each of these sterilization methods, consideration must be given to compatibility of the materials so device performance is not adversely affected as a result of the sterilization process. Also, the packaging design and materials must be carefully considered with the sterilization procedure, post sterilization handling and storage, environmental exposure during storage and shipment, and ease of handling, opening, presentation and use during the procedure.

In embodiments, interatrial pressure vent 100 can be assembled using components that have been pre-sterilized using one of the above methods or others that are well known and the final assembly may be accomplished in an aseptic manner to avoid contamination.

In embodiments, the interatrial pressure vent 100 can be supplied non-sterile and be sterilized around the time of use using one of the above methods or by other methods well known by those skilled in the art.

Similarly, the placement catheter 111 may be pre-sterilized and packaged separately from the interatrial pressure vent 100. Sterilization can be performed using a similar method to the interatrial pressure vent 100 or using a different method from the same choices or using some other method as is well known by those skilled in the art.

In embodiments, an interatrial pressure vent 100 and the placement catheter 111 can be supplied pre-sterile and in the same package. In another aspect, the interatrial pressure vent 100 and the placement catheter 111 can be preloaded and supplied pre-sterile.

Prior to insertion, the interatrial pressure vent 100 is preferably folded and stowed onto the placement catheter 111. This can be accomplished in a sterile field using aseptic techniques in the following steps. First the interatrial pressure vent 100 is presented to the sterile field and the placement catheter 111 is presented to the sterile field. Second, the interatrial pressure vent 100 and placement catheter 111 are inspected for visible signs of damage, deterioration or contamination. Third, the second handle component 129 of the placement catheter 111 is refracted fully so the outer shaft 113 exposes the inner shaft 112 to the maximum extent allowed. Fourth, the interatrial pressure vent 100 is positioned in the correct orientation over the inner shaft 113 of the placement catheter 111 with the inner shaft 113 oriented through the center of the flow control element 104. Fifth, the flange segments 102 a-h and 103 a-h are folded away from each other and the flange segments 102 a-h and 103 a-h and the core segment 106 are compressed radially to fold the interatrial pressure vent 100 into a size and shape that will fit over and onto the waist section 120 of the inner shaft 112 with the distal ends 115 of flange segments 102 a-h aligning with the proximal groove 114 of inner shaft 112.

In embodiments comprising a flange as described in FIG. 11A the flange segments 102 a-h and 103 a-h are folded away from each other and the flange segments 102 a-h and 103 a-h and the core segment 106 are compressed radially to fold the interatrial pressure vent 100 into a size and shape that will fit over the flange 3000 described on FIG. 11A. This folding may be accomplished with the aid of an insertion tool (not shown) that retains the interatrial pressure vent 100 in a stowed position on inner shaft 112 and then advancing outer shaft 113 over the stowed interatrial pressure vent 100 and displacing the insertion tool, thereby leaving the outer shaft 113 completely covering the interatrial pressure vent 100 and mating with the distal tapered tip 140 of the inner shaft 112. In other embodiments, this can be accomplished by hand using the fingers of one hand to hold the distal ends 115 of the flange segments 102 a-102 h in position at groove 114 of the inner shaft 112 and advancing the outer shaft 113 over the inner shaft 112 enough to hold the flange segments 102 a-102 h in place. Completion of the loading procedure is accomplished by progressively advancing the outer shaft 113 until it completely covers the interatrial pressure vent 100 as shown in FIGS. 11 and 11A. While the below discussion regarding placement of the interatrial pressure vent uses the placement device shown in FIGS. 9-11 as an example, the description on placement and the procedure therefore is also meant to apply to embodiments where the inner shaft comprises a flange rather than grooves.

Positioning of the loaded interatrial valve 100 and placement catheter 111 in preparation for implanting the interatrial valve 100 in the patient can be accomplished by: first gaining vascular access; second, positioning a guidewire 121 in the right atrium of the patient; third, positioning an introducer (not shown) into the patients right atrium; fourth, locating the interatrial septum; fifth, advancing the introducer through the interatrial septum and into the patient's left atrium; sixth, advancing the guidewire 138 into the left atrium; seventh, retracting the introducer; eighth, advancing the loaded placement catheter 111 and interatrial pressure vent 100 into position so the distal end and approximately half of the stowed length of the interatrial pressure vent 100 is protruding through the interatrial septum and into the patient's left atrium as shown in FIG. 13.

In embodiments, positioning of the loaded interatrial valve 100 and placement catheter 111 in preparation for implanting the interatrial valve 100 in the patient can be accomplished by: first gaining vascular access; second, positioning a guidewire 138 in the right atrium of the patient; third, advancing the loaded interatrial valve 100 and placement catheter 111 over guidewire 138 by inserting the guidewire into and through lumen 136 and advancing placement catheter 111 into the patient's right atrium; fourth, locating the interatrial septum; fifth, advancing the placement catheter 111 through the interatrial septum and into the patient's left atrium so the distal end and approximately half of the stowed length of the interatrial pressure vent 100 is protruding through the interatrial septum and into the patient's left atrium as shown in FIG. 13.

Implanting interatrial pressure vent 100 into a patient can be accomplished, once the loaded interatrial pressure vent 100 and placement catheter 111 are in position as shown in FIG. 14, by first, retracting first handle component 128 toward second handle component 129 while holding second handle component 129 until flange segments 103 a-h are fully uncovered as shown in FIG. 15, and as can be verified by visualizing the markers 119 using fluoroscopy or using echocardiography; second, retracting the placement catheter 111 with partially deployed interatrial pressure vent 100 toward the patient's right atrium until the flange segments 103 a-h are in contact with the left atrial side of the interatrial septum, as shown in FIG. 16, and as can be verified using the same techniques mentioned or as can be perceived by the user based on the resistance felt against further proximal movement of the placement catheter 111; third, continuing to retract the outer sheath 113 by retracting first handle 128 toward second handle 129 until the outer sheath 113 is retracted beyond the proximal end of groove 114 of inner shaft 112 and also uncovers flange segments 102 a-h, at which time the flange segments 102 a-h of interatrial pressure vent 100 will deploy returning to the preloaded geometry and capture the interatrial septum between the flange segments 103 a-h and flange segments 102 a-h as shown in shown in FIG. 18; fourth, the inner sheath is retracted through the flow control element 104 of interatrial pressure vent 100, into the patient's right atrium as shown in FIG. 19; fifth the first handle component 128 is advanced away from the second handle component 129 to reposition inner shaft 112 into the position relative to outer shaft 113 it was in during placement and the placement catheter is removed from the patient and the procedure is completed.

In other embodiments, implanting interatrial pressure vent 100 into a patient can be accomplished, once the loaded interatrial pressure vent 100 and placement catheter 111 are in position as shown in FIG. 14, by first, advancing second handle component 129 toward first handle component 128 while holding first handle component 128 until flange segments 103 a-h are fully uncovered as shown in FIG. 15, and as can be verified by visualizing the markers 119 using fluoroscopy or using echocardiography; second, retracting the placement catheter 111 with partially deployed interatrial pressure vent 100 toward the patient's right atrium until the flange segments 103 a-h are in contact with the left atrial side of the interatrial septum, as shown in FIG. 16, and as can be verified using the same techniques mentioned or as can be perceived by the user based on the resistance felt against further proximal movement of the placement catheter 111; third, continuing to retract the outer sheath 113 by advancing second handle 129 toward the first handle 128 until the outer sheath 113 is retracted beyond the proximal end of groove 114 of inner shaft 112 and also uncovers flange segments 102 a-h, at which time the flange segments 102 a-h of interatrial pressure vent 100 will deploy returning to the preloaded geometry and capture the interatrial septum between the flange segments 103 a-h and flange segments 102 a-h as shown in shown in FIG. 18; fourth, the inner sheath is retracted through the flow control element 104 of interatrial pressure vent 100, into the patients right atrium as shown in FIG. 19; fifth, the second handle component 129 is retracted away from the first handle component 128 to reposition inner shaft 112 into the position relative to outer shaft 113 it was in during placement and the placement catheter is removed from the patient and the procedure is completed.

For a variety of reasons, it may be necessary or desirable to remove interatrial pressure vent 100 and placement catheter 111 during any part of the procedure without further risk or injury to the patient. This is possible as follows: if, for any reason, it is desired for the device to be removed before outer shaft 113 is retracted and flange segments 103 a-h are deployed, then the placement catheter 111 with interatrial valve 100 can simply be retracted out through the same pathway as introduced.

If, following deployment of flange segments 103 a-h it is necessary or desirable to remove the device, then the interatrial valve 100 can be retracted into the placement catheter 111 by advancing first handle 128 away from second handle 129, while holding second handle 129 stationary, thereby advancing outer sheath 113 distally through the interatrial septum and over the flange segments 103 a-h. In embodiments, radiopaque markers 118 placed in marker holes 109 are captured in groove 114 (see FIG. 17) and cannot fit in the gap between waist 120 of inner shaft 112 and inner surface of outer shaft 113, so as outer sheath 113 is advanced, flange segments 103 a-h are forced to fold inward toward their stowed position and are retracted back onto inner shaft 112 and within outer sheath 113. Once outer shaft 113 is fully advanced, catheter 111 can be refracted as shown in FIG. 17 to be removed out through the interatrial septum and out through the same pathway as introduced.

FIG. 19A is an embodiment designed to enhance the retrievability of the device. The procedure for implanting the device is substantially similar to that which is described above; however, there are variations to the placement catheter and the device, which will be described below. As discussed in connection with FIGS. 7A through 7C, embodiments of the interatrial venting device comprise at least one flange segment being longer than the other flange segments. The embodiment schematically shown in FIG. 19A preferably works with such embodiments having at least one flange segment that are longer in relation to the other flange segments; thus the segments shown in the RA have the same reference number as the longer segments in FIGS. 7A through 7C, i.e., 102L. In embodiments utilizing the techniques shown in FIG. 19A, the opening 113 a of outer sheath 113 of placement catheter is angled or has a more surface area on one side relative to the other. The placement catheter is oriented during the procedure such that the angled opening (or the plane of the opening itself) is at an angle more normal to the septal wall 107. In the embodiment shown in FIG. 19A, that angle appears to be around 45 degrees with respect to the septal wall 107, but any angle which provides an more normal angle with respect to the septal wall may be used, and any opening which provides more surface area of the outer sheath 113 on one side with respect to the other side may be used. Reference numerals 4000 through 4050 refer to steps in the process described below. The process is largely similar to that described above or with respect to any well-known placement catheter system and process, therefore only the applicable differences will be described. As can be seen at steps 4000 through 4020, the placement catheter is positioned and the device is in the beginning stages of deployment. At steps 4030 and 4040, the as the outer sheath 113 is retracted and on the RA side (or when the inner shaft is advanced while the outer sheath is on the RA side, which is not shown), the opening allows one of the longer flange segments 102L to be deployed after other flange segments have been deployed and are thus in contact with the septum 107. The at least one longer flange segment 102L is retained in the placement catheter system by way of the outer sheath 113, the length of which extends further on one side than the other due to the opening and thus covers the longer segment 102L while the other shorter segments have been deployed. In this way, the operator of the placement catheter can determine if the interatrial device is in the proper position. If not, the operator can still retrieve the device up until the last point prior to full deployment, i.e., when at least one of the longer flange segments (102L for example) is still retained in the placement catheter by the outer sheath 113. If it is in proper position, the deployment may commence.

Another deployment embodiment is now described in connection with FIG. 19B. This deployment embodiment may be used with any embodiment of the interatrial vent described herein. Reference numerals 5000 through 5050 refer to steps in the process described below. At step 5000, the LA side of the device (generally referred to in this figure as 100) is deployed on the LA side of the heart. Further deployment is shown at step 5010 and the outer sheath is retracted into the RA side of the heart, which allows flow control element 104 to exit the placement catheter. Placement catheter is equipped with a balloon, which is in fluid communication, for example, with lumen 136 described above or guide wire 138. The skilled artisan will appreciate other configurations in which a balloon catheter may be provided in the placement catheter system. Upon deployment of the LA side flange or shortly thereafter, balloon 139 is inflated (shown in step 5020). The inflation of the balloon optionally coupled with a pulling-back motion of the placement catheter 111 holds the device 100 against the LA side of the septal wall 107 and thereby prevents the device 100 from dislodging during deployment and/or moving in a direction away from the septal wall. Step 5040 shows the full deployment of the device 100 while the balloon 139 is inflated. When satisfactory deployment is achieved, the balloon 139 is deflated and the placement catheter system is removed (shown at step 5050). Other embodiments that enhance deployment or retrieval of the device are described throughout.

Now referring to FIG. 20, an interatrial pressure vent 200 is shown. In embodiments, flange segments 202 a-h and 203 a-h can be formed with graduating length to reduce interference between flange segments 202 a-h and 203 a-h during handling, folding and loading. In embodiments, radiopaque markers 218 and 219 protrude into the inner cylindrical shape of the stowed position of the interatrial pressure vent and each flange segment 202 a-h and 203 a-h differ in length by at least the width of the radiopaque markers 218 and 219. In embodiments, each flange segment 202 a-h and 203 a-h differ in length by at least at least 1 mm. In embodiments, each flange segment 202 a-h and 203 a-h differ in length by at least 2% of the overall length of interatrial pressure vent 200 in the position shown in FIG. 20.

Now referring to FIG. 21, an interatrial pressure vent 300 is shown. In embodiments, flange segments 302 a-h and 303 a-h can be formed with alternating length to reduce interference between flange segments 202 a-h and 203 a-h during handling, folding and loading. In embodiments radiopaque markers 318 and 319 protrude into the inner cylindrical shape of the stowed position of the interatrial pressure vent 300 and alternating flange segments 302 a, c, e, and g are longer than flange segments 302 b, d, f and h, and correspondingly, flange segments 303 b, d, f and h are longer than flange segments 303 a, c, e and g by at least the width of the radiopaque marker. In embodiments, alternating flange segments 302 a, c, e and g are longer than flange segments 302 b, d, f and h and, correspondingly, flange segments 303 b, d, f and h are longer than flange segments 303 a, c, e and g by at least 1 mm. In one aspect the alternating flange segments 302 a, c, e and g are longer than flange segments 302 b, d, f and h and, correspondingly, flange segments 303 b, d, f and g are longer than flange segments 303 a, c, e and g by at least 2% of the overall length of interatrial pressure vent 300 in the position shown in FIG. 21.

Referring now to FIG. 22 and FIG. 23, the body element 401 of an interatrial pressure vent with integral thrombus filter and retrieval cone 442 is shown. In embodiments, conical struts 444 are affixed to body element 401 at attachment points 446 and converge at apex 450. In embodiments, conical struts 444 comprise single beams of similar material to flange segments 402 and 403 and can be attached to the body element or formed at the same time as the body element using techniques described in this specification, and can thus be integral with the remainder of the device. In embodiments the space between adjacent struts 444 is about 2 mm. In embodiments, the space between adjacent struts 444 is about 4 mm. As can be appreciated, conical struts 444 will protrude into the right atrium of the patient after implant and spaces between conical struts will function to block the passage of solid material larger than the space between adjacent struts 444. This will provide the function of preventing emboli that are larger than the space between the adjacent struts 444 from passing from the right atrium to the left atrium.

Referring again to FIG. 22 and FIG. 23, in embodiments the shape of the conical struts 444 is not straight. In embodiments the shape of the conical struts 444 can be concave when viewed on end as depicted in FIG. 22. In embodiments the conical struts can be curved in a direction away from the chord formed between the apex 450 and the attachment points 446. In embodiments there can be a hole 451 through apex 450 large enough to receive a retrieval snare (not shown). It can be appreciated that conical struts 444 and apex 450 can be used to aid retrieval of the interatrial pressure vent from a patient at some time after the implant procedure using a method as follows: A catheter tube with an internal lumen at least as large as apex 450 can be placed into the patient's right atrium using standard techniques and imaging equipment. A retrieval snare can be fabricated from the proximal end of a guidewire bent sharply by about 180 degrees and this snare can be inserted through the catheter tube and advanced into the patient's right atrium and, with the assistance of fluoroscopy, advanced through hole 451 or around conical struts 444. Once the retrieval snare is engaged in this manner, it will be possible to retract the interatrial pressure vent by advancing a catheter tube while holding slight tension on the snare and thereby guide the catheter tube over apex 450 and onto conical struts 444.

As the catheter tube continues to advance, with some tension on the snare it will be possible to force the conical struts inward, thereby forcing the flange segments 402 to begin folding inwards. When the conical struts are nearly completely in the catheter tube, the catheter tube can be held in a stationary position and the snare wire retracted against it, thereby causing the attachment points 446 between the conical struts 444 and the flange segment 402 to be retracted into the catheter. Flange segments 402 can begin to be retracted into the catheter at this point and the distal ends of flange segments 402 can be diverted toward the patient's left atrium but will also fold inward and into the catheter. Once the flange segments 402 are inside of the catheter tube, the snare can be held stationary and the catheter tube can be advanced further, through the interatrial septum and over flange segments 403. Once the flange segments 403 are refracted into the catheter, the catheter and snare can be moved together to retract the interatrial pressure vent into the patient's right atrium and out through the pathway through which it was introduced.

Referring now to FIGS. 24 and 25 an alternate embodiment of interatrial pressure vent 500 is shown. In embodiments, flow control element 504 may be comprised of leaflets 541 a-c. Body element 501 may be comprised of core segment 506 and flange segments 502 a-1 and 503 a-1 (not fully visible in FIG. 25); the number of flange segments being a multiple of the number of leaflets. This configuration improves the symmetry of strain against the flow control leaflets and also improves the uniformity of motion by the flow control element to changes in blood flow.

FIG. 26 shows and alternate embodiment wherein the core segment 106 is ovular rather than circular and thus the core segment is a cylindroid or elliptic cylinder rather than a simple cylinder. This embodiment is more conducive to a bicuspid (or “duckbill”, bivalve, or two-leaflet) configuration for the flow control element. The duckbill configuration is generally referred to as flow control element 104 in this figure. The inventors have found that the bi-valve configuration is able to open more fully when coupled with a core segment in the shape of a cylindroid.

FIGS. 27 and 27A show another embodiment of an interatrial device having intermediate flange segments for a more secured fit against the septal wall. In embodiment, the device comprises, like many other embodiments disclosed herein, a core segment having an axial length and defining a passage. Like other embodiments disclosed herein there is a first annual flange and a second annular flange. The flanges themselves, similar to other embodiments disclosed herein, may be comprised of segments such as 102 a-h and 103 a-h as shown in FIG. 6 by way of a non-limiting example. However, embodiments with an intermediate flange comprise a flange that contacts the RA or LA side of the septum for better adherence and positioning of the device within the atrial septum. Thus, the intermediate flange may be disposed between the first annular flange and the second annular flange along the core segment axial length. Like other flanges disclosed herein the intermediate flange may be annular, and may comprise a plurality of flange segments. The flange segments of the intermediate flange have substantially similar lengths and, in embodiments, those lengths are less than the lengths of the flange segments of the first and second annular flanges. In embodiments, the intermediate flange segments are part of another a third annular flange situated on the same side of the septal wall as one of the other flanges. Reference numerals 6000 through 6040 refer to steps in the deployment of such an embodiment and will be discussed in connection with the structural features of the embodiment to illustrate this embodiment's utility and operation. The deployment process is similar to those described above, and to any commonly-known catheter based delivery process and as such the details of the process will not be discussed herein. Steps 6000 to 6020 show the deployment process steps proceeding in much the same manner as described herein. At step 6030, intermediate flange segments 602 and 604 of intermediate (or third) annular flange are deployed on the RA side. In this embodiment, intermediate flange segments 602 and 604 are shorter than the majority of the flange segments of the RA-side flange. As such, segments 602 and 604 are deployed prior to other longer segments and contact the septal wall 107 at points closer to the septal opening than the contact points of the longer segments. In this manner, the intermediate segments 602 and 604 (and the flange which they comprise) provide increased stability of the device. Any number of intermediate segments may be used although it is preferable to have at least two. As with other embodiments, the stiffness of the intermediate segments may be altered so as to differ from other flange segments of the device to avoid damage to the septal wall, i.e., lesser stiffness/greater flexibility, or to provide increased stability, i.e., greater stiffness/lesser flexibility. The choice of stiffness/flexibility variations must be balanced against the desired goals.

FIG. 27A is a side elevational view of embodiment discussed in connection with FIG. 27. In FIG. 27A the pressure venting device in its stowed configuration. Flanges 102 and 103 are shown with the flange segments that comprise them (flange segments not individually labeled). Core segment is again shown as 106. At a point between the end of the core segment 106 and proximal end of the RA side flange segment 102, the intermediate segments (collectively referred to as 600) emerge. Intermediate segments may be integral with the venting device or attached thereto in the manners described above.

In other embodiments, the flow control element is configured to direct the blood flow in a desired direction. FIGS. 28A through 28C show such embodiments. In FIG. 28A interatrial device 100 is shown implanted in the atrial septum 107 of the heart in the same manner as shown in FIG. 1. Flow control element 104 is configured to aim the flow, shown in this figure as in the direction toward the superior vena cava. FIGS. 28B and 28C show a more detailed view of embodiments that enable the flow to be directed in a desired direction. As shown in FIG. 28B, flow control element may comprise a baffle-like flange 104 a that extends at a downward angle and in the corresponding direction. In use, such embodiment directs the flow downward. FIG. 28C shows an embodiment where the flow is directed upward. The valve material (e.g. material for leaflets) can be sized and secured to the 100 in manner to direct the flow. For example, the flow control element may contain a curved tubular member whose opening points toward the direction of flow, or the flow control element may otherwise comprise an opening directed at the area of interest. In embodiments with baffles, the stiffness of the baffle 104 a may be varied, for example, made stiffer. The length of the baffle can also be varied depending on the desired flow direction. The baffle can be a separate member attached to the flow control element or it may be made of the material and/or integral with the remainder of the flow control element.

FIGS. 29A through C show exit profile shapes of the flow control element 104. In these figures, the flow control element 104 is being viewed from the RA side and thus the direction of flow is understood to coming out of the page at an angle substantially normal to the page. If the flow control element is a valve as described herein, folding and suturing patterns may be employed to achieved these exit profile shapes. In other embodiments, the end of the flow control element may be provided with a plate, or a partially frustoconical end piece, having an opening defining the two-dimensional shape shown in the Figure. The skilled artisan will appreciate that other exit profile shapes may be fashioned. The selection of an exit profile shape may provide advantages such as directing flow, preventing thrombi from moving across the septal divide, and/or reducing injury to surrounding tissue.

Another embodiment is shown in FIG. 30. In this embodiment, the core segment 106 and flanges 102 and 103 of the device are substantially similar those described herein. Instead of the flow control elements described above (or in addition thereto) a tube-like member 700 is secured to the core segment 106. The tube member 700 is attached to the core segment 700 in a manner to allow the RA end of tube to extend into the RA in an axial direction, thus the tube's length must be sufficient to extend a distance into the RA. It has been found that the tube 700 configured in this manner prevents embolic particles from entering the tube and crossing over the septal divide into the LA. The distance that the tube 700 extends into the RA and beyond the plane of the RA-side flange opening (indicated by dotted line) should be at least a 1 mm but may be up to 2 cm in preferable embodiments. Even at relatively short lengths (such as where the tube extends only a few millimeters into the RA), the inventors have noted the surprisingly unexpected result of a reduction of embolic particles passing through. This is due to, in part, the tendency of embolic particles to collect along the surface of the septal wall and move toward the septal opening (or opening of an implanted device) with each cycle of the heart. By extending away from the septal wall 107, the tube provides an effective barrier to the embolic particles that would otherwise travel toward and possibly through the septal opening.

Placing the Interatrial Pressure Vent or Prosthesis into a Mounting Tool

FIG. 31 depicts a first embodiment of a mounting and loading tool useful for placing the prosthesis onto a catheter or other delivery device for delivery in vivo to a patient. In this embodiment, mounting tool 2001 includes a base plate 2002 with orifices 2003 for securing other components as shown with fasteners 2004 and pin 2009. The principal component is a loader body 2014, mounted via the outer two fasteners and orifices as shown. A mounting platform 2023 is mounted in the center of the loader body via the third orifice and pin 2009. Mounting platform 2023 includes a lower orifice 2026 for mounting to the loader body via the middle loader body orifice with pin 2009. Mounting platform 2023 also includes a slotted cam surface 2024. Pivot 2029 mounts to the loader body 2014 via pivot pin 2028 through pivot orifice 2030 and loader body orifice 2016. Pivot 2029 and lever 2031 mount on the left side of loader body 2014 below the side doors 2020, as seen in FIG. 31. Movement of pivot 2029 and lever 2031 on the cam surface allows a user to raise and lower the mounting platform. The two opposite positions of the mounting platform are the lower and upper positions, achieved by rotating the pivot to the desired position. In other embodiments, the cam surface may simply be a slot or groove in the side of the mounting platform 2023.

The loader body 2014 also mounts the other components of the device. The loader body includes internal side channels 2018 for mounting two side doors 2020 and also includes vertical bores 2015 and a vertical side channel 2019 for mounting top plate 2005. The side doors 2020 include a central orifice 2027 in the shape of a semicircle, for closing against the prosthesis, discussed below. The side doors include shelves 2021 on either side for riding against the channel 2018 of the loader body. The side doors each also include a retaining pin 2022. The pins protrude through side windows 2017 in the loader body and allow the side doors to slide within the loader body while preventing their complete removal from the assembly.

Top plate 2005 includes a top surface 2006, an adjustable internal iris 2011, which functions much like the iris in a camera. The iris has sections that adjust inward and outward to open and to close the central opening of the iris. The adjustable iris decreases the area of the opening and closes in a manner that allows the top section of the implantable device to rest on top of the partially or full closed iris. Opening and closing of the iris is controlled by control lever 2013. The top plate includes two vertical rods 2007 for mounting in the vertical bores 2015 of the loader body and also includes a vertical side guide 2008 with an elevating mechanism 2010 actuated by a top thumbwheel 2012. Raising and lowering via the elevating mechanism allows the user to raise and lower the iris and thus adjust the separation of the left and right flanges of the prosthesis with the iris.

The mounting and loading assembly is used in the following manner. The loader body is positioned conveniently for the user, with the top plate removed and with the doors open. A prosthesis, such as prosthesis 100, is placed on the loading platform, with the left atrium legs or flange facing downward and with the loading platform in the lower position. The doors 2020 are then closed, with the mounting platform still in the lower position, thus placing the left atrium flange below the doors. The mounting platform 2023 is then raised to its upper position by rotating pivot 2029, causing the lower portion (left atrium flange or legs) to be pressed against the underside of the doors 2020. While not shown in FIG. 31, this movement causes the legs of the left atrium flange to be radially spread out.

At this point, the top plate is assembled to the mounting and loading tool and a catheter, such as one of the catheters depicted above in FIGS. 10-12, and also described above, is introduced though the center of the prosthesis. The portion inserted includes the catheter tip and a portion of the catheter control wire connected to the tip. The position of the catheter is adjusted so that the right atrium ball (“RA ball”) or other retention device is vertically aligned with the right atrium flange, as discussed above with respect to FIG. 11A. The iris is then partially closed. Vertical alignment may be achieved by raising the top plate 2005 using handwheel 2012. With the doors 2020 closed and the left atrium flange trapped below the doors, raising the top plate will stretch the prosthesis, separate the left and right atrium flanges, and also stretch the prosthesis over the catheter. In one embodiment, the diameter of the orifice made by the two half-circular cut outs 2027 of the side doors is about equal, or slightly less than, a diameter of the catheter intended for use as a delivery device for the prosthesis discussed herein. The diameter may range from about 3 mm (9 Fr) to about 7 mm (21 Fr).

As the iris is raised, the upper (right atrium) flange will approach the retention device, such as the RA ball and the outer sheath of the catheter. The iris may continue to be closed while the top plate is raised, thus bringing the RA flange into contact with the RA ball. If the mounting platform 2023 has not been fully raised, it may also be raised gradually during this process. The entire sequence may be achieved by sequential use of the mounting platform 2023 and pivot 2029, the iris 2011 and handle 2013, and the elevating mechanism 2010 and thumbwheel 2012. When the RA flange has closed over the RA ball, the outer sheath may then be brought over the RA flange, securing the end of the prosthesis in the outer sheath. At this point, the iris 2011 may be opened along with doors 2020 and the catheter and prosthesis removed from the mounting and loading tool. The inner wire, firmly attached to the catheter tip and RA ball, is then retracted, pulling the central portion of the prosthesis and the LA flange into the outer catheter.

The catheter is then processed as discussed above, including assembly to a control device or handle, packaging, and so forth. This process is desirably performed in a sterile environment, with all components, tools, fasteners, and so forth, scrupulously clean and sterile before and during all steps of the process. The mounting and loading tool depicted in FIG. 31 and described above is desirably made from an inert, lubricious and medically-acceptable plastic material, such as a fluoropolymer, fluorinated ethylene-propylene, PTFE, UHMWPE, acetal, polycarbonate, and so forth.

In addition to the mounting and loading tool discussed with respect to FIG. 31, there are other embodiments for mounting a prosthesis and for loading a prosthesis onto a catheter or delivery device. Additional embodiments of useful tools are discussed below. In the discussion below, FIGS. 32-34 concern a discrete mounting tool, while FIG. 35 concerns a separate tool for loading a mounted prosthesis onto a loading tool.

FIG. 32 depicts a mounting tool 2500 useful for mounting a prosthesis for relieving intracardial pressure for a mammal, such as a human. The mounting tool includes four principal components. The principal components include a mounting plate 2501, a star-shaped cutout plate 2511, a lower flat disc 2521, also known as a right atrium or RA disc, and an upper counterbored disc 2531, also known as a left atrium or LA disc. The four components are used and stacked in the manner depicted in the drawing, in combination with a prosthesis mounted on the tool. All four components are desirably made from a lubricious, non-allergenic, medically-acceptable plastic, such as a fluoropolymer, fluorinated ethylene-propylene, PTFE, UHMWPE, acetal, polycarbonate, and so forth.

Mounting tool 2500 includes mounting plate 2501 having a cylindrical bottom disc 2503, the disc having a central raised portion 2505 and an additional raised portion 2507 atop the central raised portion. Plate 2501 also includes a plurality of inserts 2502 for attracting and joining with a similar number of inserts in cutout plate 2511. The inserts may be magnets or a combination of magnets and magnetically-attractive materials.

Star-shaped cutout plate 2511 includes a flat top surface 2512 with a cutout in a general shape of a star 2515. While the cutout has the general shape of a star, it is understood that the shape need not be a perfect star with perfectly equal sides and perfect angles between all legs or sides of the star. For example, the tips and corners of each point of the star are rounded rather than sharp. This avoids scratching the prosthesis and also avoids any scratching of personnel assembling the prosthesis to a catheter. A cutout in a general shape of a star is sufficient to accomplish the task described herein. The skilled artisan will appreciate that the shape would be appropriate for accommodating the shape of the device.

The bottom surface includes a counterbore 2514 for most of the entire bottom surface. A counterbored surface typically has an abrupt or right-angle termination, such as achieved by molding or by machining with an end-mill or other flat-bottomed tool. The counterbored surface is preferable to a more gradual change, such as a funnel-shaped countersink or angled approach. As discussed below, the counterbored surface of the cutout plate is used to mount the cutout plate to a loading tool. Thus, having the walls of the counterbore straight rather than angled is helpful, because with sufficiently close tolerances, the counterbore aids in firmly securing the cutout plate to the loading tool used. It is possible, however, that angled walls, i.e., a countersink, may be used instead. Cutout plate 2511 also includes a plurality of inserts 2502 matching the plurality of inserts in mounting plate 2501. In one embodiment, the inserts are polar magnets, i.e., N-S magnets with the poles arranged so that the discs can only be joined in one way.

For example, mounting plate 2501 may have eight N-S magnets molded into the plate with the north poles on the top side, with the raised portions. If cutout plate 2511 has the magnets similarly mounted, north poles on top, south poles on bottom, then the south poles on the bottom of cutout plate 2511 will attract the north poles on the top side of mounting plate 2501, and the two plates may be joined. Because of the polar orientation, there will be no magnetic attraction if one tries to assemble the discs in the incorrect manner, i.e., with the counterbored surface on top. In another incorrect orientation, with the cutout plate 2511 below mounting plate 2501, the plates will be magnetically attracted for assembly, but the star-shaped feature 2515 will be positioned away from the raised portions 2505, 2507. A user will not be able to position the prosthesis on the mounting tool using both the raised surfaces and the star-shaped cutout. Thus the mounting plate 2501 and the cutout plate 2511 have been designed for assembly and for fool-proof assembly.

Right atrium disc or lower flat disc 2521 is made as a two-part assembly, a right half 2522 and a left half 2523. There is a central orifice 2525 and the disc has a chamfer or bevel 2526 on its side. Each side of each half has three bores 2527 within the disc and perpendicular to a radius of the disc, the three bores on each side used to assemble the halves. In one embodiment, the outer two bores are used for magnets to attract the halves together and the central bore is used for a dowel to align the halves. Thus, in one embodiment, right half 2522 has three bores 2527 as shown, the central bore being merely a void for accepting a dowel from the left half, and the two side bores filled with two north-south magnets with the south poles facing outward. Left half 2523 has three bores 2527 on each side, the central bore on each side filled with a protruding dowel 2528 and the two side bores filled with two north-south magnets with the north poles facing outward. Use of the dowel and the void may be considered as a male-female joint. When the two halves are brought into contact, the opposite poles of the magnets will attract and the two halves will be firmly joined.

The left atrium disc 2531, also known as the upper counterbored disc, is also formed as two halves, right half 2532 and left half 2533. Counterbored disc 2531 has a counterbore 2534 on top, the counterbored or void portion removing material from a majority of the top surface. There is a chamfer or bevel 2536 on the side of the disc toward the bottom, such that when counterbored disc 2531 is assembled with lower flat disc 2521, there is a “V” in profile, the “V” formed by the bevels or chamfers on the two discs. Counterbored top disc 2531 also has a central bore 2535 of about the same diameter as central bore 2525 of lower flat disc 2521. Each side of the halves includes three bores 2537 within the disc, the bores perpendicular to a radius of the disc. The bores are voids for accepting devices for joining the two halves, as discussed above for the lower flat disc. In one embodiment, the central bores include a dowel and a void for aligning the two halves, while the outer bores include magnets 2502 with oppositely-facing poles for attracting each other. The dowel and void function for assembly as a tab and a slot in both the right and left atrium discs 2521, 2531. The bores may themselves be considered a slot, for use with a dowel, a tab, a magnet or a magnetic material. The tabs may be made of a plastic material or may be made of durable stainless steel or other non-corroding, medically-acceptable material.

In other embodiments for the side bores on either the lower plate 2521 or the upper counterbored disc 2531, the inserts could include magnets on one half and steel or iron bars on the other half, or one magnet and one steel bar on each half, with a facing magnetically-attractive metal and magnet on the other half.

In one embodiment, the lower flat disc 2521 may be made a different height than the height of the upper counterbored disc 2531. The difference in heights makes it unlikely that an improper assembly could occur between one half of the lower flat disc and one half of the upper counterbored disc. In one embodiment, the magnets of the halves with the central dowels may be assembled with the north poles outward, while the magnets of the halves with the central voids may be assembled with the south poles outward. This would make mis-assembly of the lower flat disc 2521 and the upper counterbored disc 2531 very difficult, since two pieces with dowels (male portions) would be impossible to join. While the two pieces with voids may be magnetically attractive and may join to form a mis-assembly, there would only be one assembled disc, since the two halves with the dowels could not be joined. Thus, use of the magnets and dowels makes assembly of the discs virtually error-proof.

Mounting tool 2500 is used to orient a prosthesis for placement in a loading tool, as discussed below. In practice, a prosthesis for placement in a patient's heart is placed on the mounting plate 2501. In one embodiment, a right atrium (RA) flange is placed on the central portion 2505. The star-shaped cutout plate 2511 is placed atop the mounting plate 2501, with the points of the star placed atop the flange joints of the RA flange, thus locking the prosthesis in place with the oppositely-facing magnets. The left atrium (LA) flange and the barrel, or central portion of the prosthesis, now stand above the raised portions 2505, 2507 of mounting plate 2501. The right atrium disc 2521 is now joined to the assembly between the right atrium flange (lower portion) of the prosthesis and the left atrium flange (upper portion) by bringing the two halves together, such that the bevel 2526 is on the upper side of the disc 2521.

The left atrium disc 2531 is then added to the assembly atop the right atrium disc, also by bringing the two halves together. In this instance, bevel 2536 of the left atrium disc 2531 faces downward. The chamfers or bevels of the two discs are thus adjacent when the mounting tool 2500 is assembly correctly, the bevels together forming a “V” which will be used later by the loading tool, as discussed below. The mounting plate 2501 and the star-shaped cutout plate 2511 may then be removed. When the prosthesis has been placed correctly on the mounting tool and the mounting plate and cutout plate are removed, the left atrium flange protrudes from the left atrium disc and the right atrium flange protrudes from the right atrium disc, as seen in FIGS. 33-34.

The mounting tool is depicted in FIG. 33 after it has been assembled with a prosthesis 100. The mounting tool includes mounting plate 2501 with cutout plate 2511 atop the mounting plate, and with right atrium disc 2521 atop left atrium disc 2531. In this figure, prosthesis 100 is mounted with left atrium flange 103 visible on top. Note the counter bore 2534 visible in the left atrium disc 2531. This is the configuration immediately after the prosthesis has been mounted and the left and right atrium discs have been inserted to separate the left and right atrium flanges. Note also that bevels 2526 and 2536 are adjacent, forming a V when seen from the side.

In FIG. 34, the mounting and cutout plates have been removed and the assembly 2560 has been inverted, with right atrium disc 2521 atop left atrium disc 2531 and with the right atrium flange 102 of the prosthesis 100 on top. Note that the right atrium disc 2521 is flat and has no counterbore on the side seen in this view.

Loading the Prosthesis into a Loading Tool

After the prosthesis has been mounted, a loading tool may be used to assemble the prosthesis and place it into a catheter or other delivery device. A loading tool useful in this process is depicted in FIG. 35 and is herein described.

Loading tool 2600 includes a base plate 2601, side door supports 2611 and 2621, a central column 2641 and a travel subassembly 2650. The base plate, side door supports and central column each mount to the base plate via fasteners 2604, as shown. In one embodiment, the fasteners may mount through the bottom and the heads may reside in countersunk or counterbored recesses in the bottom of the base plate. The base plate also includes a travel control mechanism or thumbwheel 2606, including travel screw 2607 and spacer 2608. In this embodiment, the travel control mechanism 2606, and the thumbwheel travel adjuster are mounted within the base plate, and a portion of the handwheel protrudes through a side of the base plate. Rotating the thumbwheel allows one to advance or retract travel screw 2607 and thus raise or lower travel subassembly 2650.

Side doors 2631 are identical and reside on side door supports 2611, 2621. Main doors 2660 are also substantially identical and reside on travel subassembly 2650. In one embodiment, door supports 2611, 2621 each include a top shelf 2613 for capturing a side door and allowing it to ride back forth, to and fro. In addition, door supports 2611, 2621 also each contain a travel stop or pin 2615, 2625. The pin stands in a groove 2637 within the side door, the pin limiting travel of the door to that allowed by the grooves, e.g., the half-way mark of the central column 2641 and its concentric top surface 2643, on the one side, and retreat from the central column in the opposite direction when appropriate. In this manner, the side doors can slide back and forth symmetrically to meet each other. The side doors have a taper 2633 on their front, as well as a half-circular cutout 2635 on the front. Each side door 2631 also has a vertical pin 2636 for ease of moving the door back and forth and also limiting the forward travel, when the pin touches the shelf 2613. In one embodiment, the diameter of the orifice made by the two half-circular cut outs is about equal, or slightly less than, a diameter of a catheter intended for use as a delivery device for the prosthesis discussed herein. The diameter may range from about 3 mm (9 Fr) to about 20 mm (60 Fr).

Main doors 2660 mount atop the travel subassembly 2650 via main door mounts 2651, 2652. The main doors slide back and forth in a manner orthogonal to the side doors. In this embodiment, the main doors are somewhat larger than the side doors and are used to compress the prosthesis to a diameter suitable for a catheter with a similarly desirably small diameter for delivery to a patient. The front portion of the each of the main doors thus includes a transition 2664 to a frontal semicircular arc 2665 and a semicircular bore 2666 with a radius consistent with such a small diameter. In one embodiment, the desired diameter is about 3.3 mm or 10 Fr, and the radius of the front bore is thus about 1.65 mm. In other embodiments, the radius is from about 1 mm to about 4.5 mm, to accommodate delivery catheters from about 2 mm to about 9 mm, and for catheters with a similar diameter.

The travel subassembly 2650 mounts to the loading tool via an internal threaded bore 2657 that interfaces with threaded screw 2607. Movement of the thumbwheel 2606 moves travel subassembly 2650 up and down as desired. Travel assembly 2650 includes door mounts 2651, 2652 including tongues 2654 atop the mounts and pins 2653 for limiting travel of the main doors. The main doors 2660 are substantially identical and include a groove 2661 along their length of their bottom. Tongues 2653 ride within grooves 2661 of the main doors.

The main doors also include locking pins 2663. Each pin may be used to lock the main door 2660 into the closed position by closing the door fully and depressing the pin to engage orifice 2655 in door mounts 2651, 2652. The pins 2663 may also be used to restrain each door away from the closed position by opening the main doors and depressing the pins outside travel subassembly 2650 so that further inward travel is not possible with the pins depressed. Central column 2641 with mounting surface 2643 mounts to the base plate 2601 via a central orifice 2645 and a fastener from below the base plate. The central column is positioned symmetrically within orifice 2656 of the travel subassembly 2650. The central column and the mounting surface are stationary, while around them the travel subassembly 2650 travels vertically and side doors 2631 and main doors 2660 move horizontally.

Loading the Prosthesis Into the Catheter

The loading tool is used in the following manner, in one embodiment. Other embodiments and other methods may also be used.

The side doors and main doors are opened to their full open positions and the mounted prosthesis assembly 2560 described above is placed onto central column top surface 2643, with the right atrium flange or legs up and the left atrium flange down. Note that in this configuration, the left atrium disc 2531, which is the disc with the large counterbore 2534, faces downward. In one embodiment, the counterbore is sized and oriented to fit precisely onto top mounting surface 2643 of the loading tool 2600, discussed below. Top surface 2643 is the mounting or loading surface for placing the mounted assembly 2560 into the loading tool 2600.

Once the mounted assembly 2560 is placed into the loading tool 2600, the travel subassembly 2650 is raised or lowered so that the side doors align with the “V” formed by the bevels or “V” of the mounted assembly. The side doors 2631 are then closed, bringing the tapered front portions of the side doors into contact with the “V” and urging apart the left atrium and right atrium discs of the mounting tool. The main doors 2660 are then closed against the side doors 2631.

Once this has been accomplished, a delivery catheter 2040 is assembled to the prosthesis, as depicted in FIG. 36. A clear loading tube 2561 is moved over the outer sheath 2563 and the tip (not shown in FIG. 36) of the catheter 2040 is inserted through the central bore of the mounted assembly 2560. Visible in FIG. 36 is the inner sheath 2565, inner control wire 2569 and right atrium ball 2567. As seen in the figure, the right atrium ball 2567 should be aligned with the right atrium flange 102. The thumbwheel 2606 is then adjusted so that the main doors 2660 are above the side doors 2631, such that the main doors 2660 can close. As the closed main doors are raised using thumbwheel 2606, the right atrium disc 2521 will rise, and the right atrium flange 102 will begin to lengthen axially and compress radially. It may be advantageous to insure that no legs or struts of the flange are intermingled or caught in the disc or the doors as the doors rise. Thumbwheel 2606 is used to raise the main doors while the catheter is held in a position that allows the right atrium flange to close around the right atrium ball 2567. When this operation has been correctly accomplished, the legs or struts of the flange are evenly and tightly spaced around the right atrium ball or flange.

The prosthesis is now brought into the catheter. In one embodiment, the following procedure is used. The RA ball acts as a compression device, compressing the right atrium flange. After the right atrium flange is firmly compressed around the right atrium ball, the outer sheath 2563 is held firmly while the inner sheath 2565 and control wire 2569 are pulled back. This pushes outer sheath 2563 over the right atrium flange and ball 2567. The ball 2567 should be pulled into the outer sheath 2563 so that it, and the right atrium flange, are no longer visible. The travel assembly 2650 is now lowered, using the thumbwheel, until it just touches the side doors 2631 (not shown in this view). Both sets of doors are opened and the catheter 2040 and left and right atrium discs 2631, 2621 are removed from the loading tool 2600. The left and right atrium discs are then removed from the catheter by pulling them apart.

The left atrium flange is now lengthened axially and compressed radially. In one embodiment, the clear loading tube 2561 has a larger diameter than the outer sheath 2563. The clear loading tube 2561 is slid over the left atrium flange 103, pushing the left atrium flange legs together. The clear loading tube should be slid forward or distally until it completely covers the prosthesis. The control wire 2569 is then pulled proximally, pulling the inner sheath 2565 and pulling the prosthesis into outer sheath 2563. The clear loading tube 2561 is then removed. The above mounting and loading procedures are accomplished in a sterile environment. Alternatively, the devices and components may be sterilized or re-sterilized after assembly.

Any other desired components, such as an outer shipping sheath, may then be added. In one embodiment, an outer shipping sheath is added in a sterile manner, as shown in FIG. 37, over the outer sheath 2563. Sterile outer shipping sheath 2571 with connector 2573 and visible cap 2575 is added over the outer sheath 2563 in such a way that inner sheath 2565, right atrium ball 2567 and right atrium flange 102, the central portion of prosthesis 100, left atrium flange 103, inner control wire 2569 and tip 2570 are visible from the outside of sheath 2571. In the embodiment shown, the prosthesis, including the right atrium flange 102 and right atrium ball 2567, has been advanced using the control wire 2569, or the outer sheath 2563 has been retracted, to allow visibility from the outside of the device. The catheter 2040, with the prosthesis loaded and ready for inspection and deployment, is now ready for shipment to a hospital or other care-giving institution.

Implanting and Deploying the Prosthesis

With this embodiment, and in this configuration, a physician can immediately inspect the prosthesis and determine whether the prosthesis is suitable for implantation into a patient. For example, the physician can immediately inspect, without even opening the outer package, whether the legs or struts of the right atrium flange are intertangled. The physician can also determine whether the left atrium flange or center portion are also suitable for implantation into the patient.

As noted, the shipping sheath is advanced over the outer sheath 2653 of the delivery of deployment catheter 2040. Accordingly, the prosthesis 100 remains within the outer sheath at all times during shipping and during removal of the shipping sheath. In some embodiments, the outer catheter is connected at its proximal end to an irrigation system, described below, suitable for irrigating the outer sheath, and thus the prosthesis, with sterile fluid, a radiopaque dye, or other desired solution. A physician can thus remove the shipping sheath, flush the prosthesis with sterile solution using the irrigation system, and move the prosthesis back and forth within the outer sheath. This allows the physician to remove any possible bubbles from the device and the catheter, at the same time allowing the physician to test the level of effort required to advance and retract the prosthesis or the outer sheath with respect to each other.

More Control Systems for Deploying the Prosthesis

A control system, including a control device or handle, and an irrigation system, may also be usefully employed with the catheter described above. One example of a control system or handle was given above in FIG. 12, and also explained. Another example is depicted in FIGS. 38A and 38B, control system 2700, including control handle 2701 and irrigation system 2720. The control handle 2701 includes a housing or grip 2713 and a control trigger 2715 for a user to retract the outer sheath or advance the inner control wire. The tension or pull required for the trigger 2715 is set with trigger spring 2731. Thus, spring 2731 controls the force needed by the user to deploy the prosthesis, i.e., the force required to release the implant onto the septal wall.

The inner control wire is grounded to the control handle through first plate 2711 via the flange 2041 of the inner control wire and may also be secured with adjustment screw 2715. The position of the first plate within the handle is set by a pin and bore, or set screw or other arrangement (not shown). The second plate 2717 is connected to the outer sheath and the irrigation system, which are secured to the second plate via connector 2722. The second plate is connected via a slot (not shown) on its rear face to a pin (see FIG. 38B) on the actuation mechanism within the handle. The first and second plates 2711, 2717 have slots or mortises on their rear faces for riding on a tenon or shelf 2716 on the side of the front grip cover 2714.

FIG. 38B depicts the internals of the trigger mechanism. Grip 2713 also includes a front cover 2714. The front cover 2714 is assembled to the grip 2713 through fasteners 2724 and orifices 2726 in the grip 2713 and mating parts 2721 in the cover 2714. The mating parts may be molded-in nuts, threaded surfaces, or other appropriate joining components.

The internals of the trigger mechanism are largely contained within the grip 2713. These include a trigger spring 2731, grounded between the trigger 2715 and a pocket in grip 1713. As noted, spring 2731 determines the pull required to activate the trigger. This spring also provides a return for the trigger to its resting or neutral position after each pull by the user. Mounted within a channel 2734 in grip 2713 are a vertical braking/release bar 2735, vertical driving bar 2737 and a driven horizontal bar 2738. Trigger 2715 also has an internal rectangular bore (not shown) for accommodating driven horizontal bar 2738.

Driven bar 2738 in one embodiment has a rectangular cross section, while the driving and braking/release bars 2735, 2737 have bores with rectangular cross sections and are mounted around the driven bar via the rectangular bores. Bar 2738 has a square cross section in one embodiment, as do the matching bores in the braking and driving bars. Other configurations may also be used for the bars 2735, 2737 and 2738, and the corresponding bores. Driven bar 2738 includes a pin 2739, which is connected directly to a bore (not shown) on the rear of the second plate 2717. Biasing spring 2733 is grounded between the driving bar 2737 and braking/release bar 2735, which is somewhat longer than driving bar 2737. Biasing spring 2733 maintains compression and separation between the braking and advancing bars. Trigger 2715 is also mounted around the driven bar 2738 via a rectangular bore in this embodiment. Other embodiments may include different geometries for driven bar 2738 and the corresponding bores in the trigger, the driving bar and the release/braking bar. These shapes may include rounded rectangular, ovate and others.

Compression spring 2712 biases the braking/release bar 2735 to a braking position by maintaining contact between the braking/release bar 2735 and driven bar 2738. Release pin 2736 protrudes above the top of the grip 2713 and is used by the operator to release the driven bar from the braking and driving bars. When a user wishes to return the second plate 2717 to a forward position, or to select a position for the second plate, the user simply presses on pin 2736. Pressing on pin 2736 has the effect of pushing the release/braking bar 2735 to the rear by overcoming the compression of spring 2712. Releasing the braking bar 2735 enables easy manual movement of the driven bar 2738 and thus second plate 2717 and the outer sheath of the catheter.

The trigger mechanism works in this manner, although many other embodiments are also possible, as also discussed in U.S. Pat. No. 7,699,297. When the user activates the control mechanism by pulling the trigger, the driven bar 2738 moves to the rear, to the right in FIGS. 38A and 38B, as does the connected second plate 2717. The outer sheath is also connected to the second plate, and as the second plate moves to the right or rear, the outer sheath does also, thus pulling the outer sheath in a proximal direction and exposing more of the prosthesis and the inner control wire. The distance traveled by the activating bar is determined by outer dimensions of the driven bar, the height of the bore in driving bar 2737, the distance between the driving bar 2737 and the braking/release bar 2535, and length of the vertical distance in the bore of trigger 2715. These lengths or distances determine the angles between the various components and thus limit the distance that is traveled by the trigger, the driving bar and the driven bar, on each pull of the trigger. Thus, each pull of the trigger moves the driven bar 2738, the second plate 2717 and the outer sheath of the catheter 2653 a predetermined distance. This makes it straight-forward for the medical professional to deploy the prosthesis. Each pull of the trigger will retract the outer sheath or advance the control wire a known and repeatable distance.

Returning to FIG. 38A, the outer sheath 2653 is grounded to the second plate 2717 via connector 2722, which provides both a mechanical connection to the control device through second plate 2717 and also a fluid connection to irrigation system 2720. The connector 2722 connects to the irrigation system 2720 through tubing 2723 to a three-way valve 2725. The valve may also include other tubing connections 2723 or to one or more connectors (not shown), and one or more optional caps 2727. As noted above, the irrigation system may be used by the physician to flush the prosthesis and outer sheath with sterile fluid before use, and to check for and remove and bubbles in the catheter and in the prosthesis. Such fluid will exit at the far end of the outer sheath 2653 after connector 2573 and cap 2575 are removed.

In one embodiment, the control system 2700 includes an internal mechanism that determines the amount of movement of the first or second plate when the trigger is pulled, and thus when the outer sheath is retracted or in the control wire and prosthesis is advanced. As noted, the amount of force needed for a single trigger actuation may be set by spring 2731. The remaining internal mechanisms, as discussed above, sets the distance traveled. The catheter is advanced to a point where the catheter and the prosthesis are in the desired location within the patient, as determined by the radiopaque methods described above, or by other desirable, reliable method.

The tip of the catheter is advanced through a surgically-created opening in the atrial septum. The tip is thus in the left atrium at the start of the deployment process. When the trigger is pulled, the outer sheath is retracted a distance sufficient to remove the outer sheath from around the left atrium legs and flange. In embodiments, this distance is about 7 mm. At this point, the left atrium legs are deployed inside of the left atrium, similar to FIG. 27, step 6000, which shows the left flange legs deployed from the outer sheath of catheter 111 into the left atrium. The entire catheter system is then pulled back such that the left atrium legs contact the septal wall, as seen in FIG. 27, step 6010. At this point, the central portion of the interatrial vent and the right atrium legs and flange are still retained by the outer sheath. The central portion, still retained, is located in the septal opening. The right atrium legs, still retained, are located in the right atrium. A second pull of the trigger retracts the outer sheath a distance, about 7 mm, to remove the outer sheath from around the central portion and the right atrium legs, thus deploying the central portion and also deploying the right atrium legs in the right atrium.

While 7 mm is a central value, the actual value may vary from about 3 mm to about 11 mm. In other embodiments, other travel ranges may be used. It will also be understood that this distance may vary, due to tolerance stack ups of the several components, including those of the catheter and the control device.

At this point, the prosthesis has been deployed, and the physician will normally inspect the deployment by one or more of the non-invasive techniques described above to insure correct placement. If deployment is satisfactory, the physician may remove the catheter and all components, including the tip, the outer sheath, the control wire, and so forth, and finally the guide wire used.

During implantation, the physician may use the catheter fluid system to determine the precise placement of the end of the outer sheath and thus the prosthesis. After the device has been advanced through the patient to a point near to the desired implantation point, the radiopaque markers on the left or right atrium flanges or the catheter may be used, along with fluoroscopy, echosound or other non-invasive means, to determine the location of the device within the patient. In addition to, or instead of the radiopaque markers, the irrigation system may use a radiopaque solution, such as a barium solution or other radiopaque solution.

The control device or handle of FIGS. 38A and 38B is merely one example of a delivery or deployment device and control device, as discussed herein, for use with a delivery catheter. Other control devices may also be used, such as additional examples depicted in FIGS. 39A, 39B and 40.

Another embodiment of a control device is depicted in FIGS. 39A and 39B. In this embodiment, as seen in FIG. 39A, control device 2790 connects to delivery catheter 2788 for delivering a prosthesis. Control device 2790 includes a control body 2791 and a control handle 2792. The control body 2791 is attached or connected to the outer sheath 2784 via connector 2797. The moveable control handle 2792 is attached or connected to an inner control wire 2786 (not visible in FIG. 39A) via connector 2799, and as seen in FIG. 39B, connected to the deployable prosthesis 2780. Connector 2798 is a fluid connector for supplying fluid to the inside of catheter 2788 and the inside of outer sheath 2784. The fluid may be sterile fluid, or may be a sterile radiopaque fluid. Control handle 2792 is equipped with a thumb ring 2794, while the control body 2791 includes two finger rings 2796. Handle 2792 is also equipped with a protruding bump or tab 2793, which is sized and designed for sequential positioning in orifices 2795.

In the sequence depicted in FIG. 39B, control body 2791 remains stationary, as does outer sheath 2784, while the control handle 2792 moves progressively to the left, i.e., in a distal direction, in a series of discrete steps, as shown. As the tab 2793 moves to the left, from the first of the orifices 2795, on the right to the last orifice on the left, the tab is visible in one orifice after another, as shown. At the same time, distal tip 2785 also moves progressively to the left, distally, to sequentially deploy more and more of prosthesis 2780. In the middle two views, left atrium flange 2787 is first partially deployed and then fully deployed. In the final view, both left and right atrium flanges 2787, 2789 are deployed. The final view also allows a close-up of the delivery catheter details, including tip 2785 and non-invasive imaging markers 118 on the tip 2785, just proximal to the tip, and just distal of the deployed prosthesis 2780.

In this handle, the control handle 2792 advances control wire 2786 and thus the prosthesis 2780 in a sequenced manner that is controlled by the spacing a, b, c, between the orifices 2795 of the control body 2791. In one embodiment, the distances are 16 mm, 5 mm and 11 mm, respectively. Other embodiments may use other discrete distances. These distances help the medical professional who deploys the prosthesis to more accurately position the prosthesis within the patient. The device and sequence shown in FIGS. 39A-39B uses a stationary outer sheath and a moving inner control wire and prosthesis. It is understood that the handle 2792 could alternately be attached to the outer sheath, so that the tab 2793 begins in the most distal position, as shown in the last movement of the sequence, and then the handle and tab move proximally to retract the outer sheath, thus deploying the prosthesis.

In addition, of course, non-invasive imaging is used to position the catheter outer sheath 2784 and distal tip 2785 to a desired position within the patient, i.e., with the distal top 2785 through an opening in the atrial septum of the patient. Differences between patients may also be studied, and the position of the control handle 2792 may be adjusted slightly for optimal prosthesis placement. As noted in other embodiments, markers for x-ray or echogenic imaging may be placed on the prosthesis, on the delivery device, or both, to assist in accurate placement. Using these markers, the medical professional or surgeon implanting the device may make adjustments to the position of the outer sheath, the prosthesis and the relative distances between them. The prosthesis may then be deployed as desired and the implanting catheter, with its tip, inner control wire, and so forth, retracted from the patient.

In FIG. 40, another control device 2170 includes a hollow cylindrical body 2171, with a central channel 2172. There is a series of bores 2173 for use with a set pin 2174 to set the position of a front slider 2190 with a hollowed-out portion 2191 for retaining an outer sheath or outer portion of the deployment device. The outer sheath is anchored within slider 2190 and its motion is controlled by a hand actuator 2195 with a thumb grip 2197 for use in moving the slider backward or forwards. The slider 2190 is connected to the hand actuator 2195 via an adapter 2175 and pin 2178. Thus, the slider, and the position of the outer sheath may be retained in place using a bore 2192 in the slider and retaining pin 2174, along with the hand actuator 2195.

Adapter 2175 and pin 2178 connect slider 2190, and an attached outer sheath, to the hand actuator 2195. Pin 2198, also known as a member, on the bottom surface of hand actuator 2195, restrains the movement of the hand actuator to the paths molded into the outer surface of the control device body 2171. These paths include forward track 2184, intermediate track 2182, and rear track 2179. The lengths of the forward and rear tracks are thus fixed or predetermined distances. The forward and rear tracks 2184, 1289 are generally parallel and are separated by intermediate, transverse track 2182.

The control wire of the catheter is connected to a rear retainer 2180 with one or more hollowed-out portions 2183 for securing the control wire or inner portion of the deployment device. The rear retainer 2180 is easily held in place securely and movably by a molded-in retaining nut 2181 and a threaded rod 2177. The handwheel 2176 itself fits snugly into the proximal, enlarged portion of the cylindrical body 2171. The handwheel may be pinned in position and may rotate in place to allow translation of the rear retainer 2180 and thus the inner control wire. The handwheel 2176 and the threaded rod 2177 allow fine adjustments to the position of the control wire with respect to the position of the outer sheath.

In use, the physician or other medical professional will advance the catheter using the non-invasive imaging techniques already described. The prosthesis is advanced to the point where the catheter tip is in the left atrium, while all portions of the prosthesis remain within the outer sheath. The slider 2190 is fixed in a distal position using pin 2174, the forward or most distal orifice of the series of orifices 2173, and orifice 2192 of the slider 2190. At this point, the hand actuator is at its most distal position, and pin 2198 is all the way forward, to the right in right track 2184, i.e., the most distal position.

At this point, the left flange is positioned within the patient's left atrium, still remaining with the outer sheath, and the retainer 2180 is locked in position and not moved further. The outer sheath is then retracted using the slider 2190 and hand actuator 2195, similar to step 6000 in FIG. 27. In one embodiment, the outer sheath is retracted by sliding the hand actuator 2195 straight to the rear and proximally, or to the left in FIG. 40. This movement is allowed by the rearward movement of member or pin 2198 in right track 2184. This movement is a fixed distance, until the pin strikes the rear of the long portion 2184 and the start of transverse portion 2182 of the molded-in paths and can go no further. The length of the long portion 2184 is fixed when the long portion is molded or machined into hollow cylindrical body 2171. The distance is that needed to deploy the left flange of the interatrial pressure vent or prosthesis. The distance may also be that needed to deploy the left flange and the central or valve portion. In one embodiment, this distance is about 7 mm. In other embodiments, the distance may be 5 mm, 6 mm, 8 mm, 9 mm or other desired distance.

After the desired portion has been deployed, the physician may use fluoroscopy or echosound to determine the exact position of the prosthesis with the patient before proceeding. If an adjustment is needed, the prosthesis can readily be retracted into the outer sheath for removal or redeployment at this stage, as will be seen in some of the improved designs for retrieval and redeployment described below.

If continuation is indicated, the surgeon or medical professional will then prepare to deploy the remainder of the interatrial pressure vent or prosthesis. The first step is to rotate the hand actuator 2195 a few degrees to the right so that pin 2198 is now in the other long track 2179. The transverse portion 2182 is only about twice as wide as pin 2198. Rotation of the hand actuator thus does not cause the prosthesis within the patient's heart to translate proximally or distally. The surgeon then moves the hand actuator in a proximal direction, to the left in FIG. 40, further retracting the outer sheath and deploying the right atrium flange into the right atrium of the patient's heart. The length of track 2179 is also a fixed distance, the distance fixed when the track is molded into the hollow cylindrical body 2171. In one embodiment, the distance is 8 mm, a little longer than the length of track 2184. In other embodiments, the distance may vary, as noted above. The distances, or the length of the tracks, may be tailored to fit the patient's anatomy, for example, by determining ahead of time the width of the patient's septum or the dimensions of the patient's heart.

In another embodiment, not shown, the two tracks of predetermined length may be a single length with a pin or other obstacle inserted at a desired point along the length of the track. The pin will prevent further movement of pin 2198 in a proximal direction and will stop the movement of the hand actuator 2195 after it has moved a fixed or predetermined distance, e.g., 7 mm. After the pin is removed, the surgeon or other medical professional may continue to move the hand actuator in a proximal direction along the remainder of the predetermined or fixed length of the track.

Retrieval of the Prosthesis

As described above in connection with FIGS. 19A, 22 and 23 there are situations where the deployment may not be satisfactory for any of a number of reasons, and the prosthesis may be removed from the patient. This situation may become apparent before the procedure has been completed. In some cases, the need for removal may become apparent while the guidewire and/or catheter delivery system with which the procedure was begun is still in place, such, for example, the embodiments described in connection with FIG. 19A. In other cases, it may be necessary to introduce a guidewire to begin a removal procedure, while in other cases a guidewire is not used. If the prosthesis has not been fully deployed, removal is typically accomplished by retracting the control wire attached to the prosthesis, or by advancing the outer sheath over the prosthesis. Removal is then accomplished by merely withdrawing the outer sheath and all its components. Once the prosthesis has been deployed, different techniques may be needed, as depicted herein.

Retrieval of the fully deployed prosthesis is depicted in FIGS. 41 and 42, while the tools used for retrieval are depicted in FIGS. 41, 42 and 43. The retrieval device 2750 is advanced to the desired location within the patient along a guidewire 2751. Components of the retrieval device 2750 include an outer sheath 2752, an inner sheath 2753 and a grasper 2755, such as the three-prong grasper depicted in FIG. 41. In one embodiment, the outer sheath has an outer diameter of about 21 Fr (about 7 mm) while the inner diameter is about 6.7 mm. In the figure, the grasper 2755 has caught the prosthesis 2757 with one of the three prongs 2755 a and its protruding hook or tab 2755 b. As noted, the tab 2755 b may be useful for insertion into an orifice of a prosthesis leg or strut, as seen in FIG. 2A, for retrieval of the prosthesis. In FIG. 2A, legs 103 x of the flanges meet at a juncture, an apex or an end of two of the legs. Each flange of the prosthesis includes two or more legs, usually in pairs, each pair also forming an apex where the legs meet.

It will be recognized that one or more components of the retrieval device may include radiopaque components or markers for better visibility by non-invasive techniques, such as fluoroscopy, echo-sound, and so forth. In one embodiment, one or more of the prongs of the grasper may be made of a radiopaque metal or material, such as the metals themselves or alloys of gold, platinum, palladium, tungsten and tantalum. In another embodiment, the prongs of may include one or more markers, e.g., a small dot or implant of a radiopaque material or echogenic material that will be easily detected by x-ray, fluoroscopy, echosound or other suitable non-invasive imaging technique.

In use, the retrieval device is advanced to the desired location within the patient, using non-invasive techniques and radiomarkers, echogenic markers, or other indicators on the device. The user has three controls to manipulate the device, in addition to advancing and retracting the entire device 2750, e.g., while the internal portions are contained within the outer sheath 2752. The inner sheath 2753 has a control wire (not shown) as does the grasper 2755 (control wire not shown). The retrieval basket 2758, depicted in FIGS. 42 and 43, also is advanced and retracted using its control wire (not shown), as will be understood by those with skill in minimally-invasive surgery arts. The grasper 2755, as the innermost component and nearest the guide wire, may have a micro-rail, i.e., a lumen or longitudinal cavity, to follow precisely the path of the guide wire. In other embodiments, it is possible to assemble the retriever so that an inner sheath is not used. For example, if the basket is assembled proximally from the grasper, and the grasper sufficiently distal from the basket, an inner sheath and its control wire may not be needed.

The user advances the device 2750 and outer sheath 2752 near the desired point and verifies the location. The user may then advance the inner sheath 2753 out from the outer sheath 2752. The user may then advance the grasper 2755 from the inner sheath and maneuver the grasper and the inner sheath, or the grasper or the sheath separately as desired, to grasp the prosthesis 2757 with the prongs of the grasper. There is no separate closing control for the grasper. The user simply maneuvers the grasper in such a manner that when the grasper is retracted, the prongs approach each other in a manner to grasp and retrieve the prosthesis. The control wire or control handle for the grasper in one embodiment has a locking feature that allows the surgeon to close the grasper and not be concerned about further manipulation of the grasper, except for withdrawal. In one embodiment, the grasper is a three-pronged Hobbs forceps, available from Hobbs Medical, Stamford Springs, Conn., USA. In another embodiment, the grasper or the retrieval device may also have a fluid channel for irrigating the retrieval site, much as the deployment catheter has a fluid channel.

Other graspers or retrievers may be used instead, such as those with four prongs, or even other retrieval devices, such as a single prong or tab. The single tab or prong may be in the form of a short cylinder, suitable for insertion in an orifice of the struts or legs of a flanged atrial septum implantable device, as shown in FIGS. 2A and 7B. The user maneuvers the grasper or tool so that the implantable device is hooked by one or more of the orifices, and then uses this connection to retrieve the implantable device.

In other embodiments, the implanted device may have one or more legs of the right atrium flange longer than most legs of the flange, making it easier to grasp one or more of the legs or struts, as shown above in FIGS. 7B and 7C. In these embodiments, the grasper may more easily approach the implanted device and grasp it, whether a multi-prong grasper is used, or whether a single tab or prong is used to grasp the longer leg. In other embodiments, the implanted device may have a flange more suited for retrieval, such as the conical flanges depicted in FIGS. 22 and 23. In these embodiments, it is relatively easy for a user to grasp the conical apex 450 for retrieving the implant via a grasper, as discussed above. Retrieval is more user-friendly also, since the shape of the implant lends itself to being pulled in the proximal direction, i.e., towards the outside of the body of the patient.

The inner sheath and the grasper are then refracted, as shown in FIG. 42, and the basket 2758 is deployed by advancing its control wire (not shown). Basket 2758 may be made from metal mesh, such as Nitinol or other medically-acceptable, shape-memory material. Nitinol is a good choice because it can be trained to assume the desired basket form as it deploys from the outer sheath. There may also be a barrier layer 2759 to help prevent any undesired piercings by wires or components of the prosthesis. The barrier layer may be made of a suitable medically-acceptable cloth, such as polyester (Dacron®, for example), or other material. Once the prosthesis is grasped and the basket deployed, the grasper 2755 and the prosthesis may be retracted into the basket by advancing the basket or retracting the grasper and prosthesis, or both. The basket, grasper and prosthesis are all withdrawn into the outer sheath, which may then be safely removed from the patient with the retrieved prosthesis.

As noted, basket 2858 may be made from metal mesh, such as a mesh made from Nitinol or other wires. In one embodiment, Nitinol wires may be 0.003 inches in diameter (about 0.08 mm in diameter); in another embodiment, the wires may be 0.020 inches in diameter (about 0.51 mm in diameter). Other embodiments may use flat wires or ovate-shaped wires. Basket 2759 is made from a single layer of Nitinol mesh. Other embodiments, such as the one depicted in FIG. 43, may use a basket 2760 having two layers, i.e., a basket including an inner layer 2761 folded over to form a second, outer layer 2762. The two-layer basket may be better at preventing objects within the basket from protruding outside the basket.

Retrieval Devices with Dilators

It is clear that the outer sheath of a retrieval device, and all components, should be as small and as thin as possible for patient comfort. Accordingly, in one embodiment, the outer sheath has an outer diameter of about 18-20 Fr. In one embodiment, the deployed basket has a largest outer diameter of about 20 mm, which is quite large compared to a 20 Fr outer catheter outer diameter. In other embodiments, the sizes may be larger or smaller, as needed. It is clear from inspection of the basket in FIGS. 42 and 43 that the space used to accommodate devices for retrieving the prosthesis will be somewhat greater than the space typically used to deploy the prosthesis.

In order to ease the transition, a retrieval device may use a dilator on its distal end. While the tip is nominally termed a dilator, it does not expand, rather its purpose is to maintain the dimension of its widest portion while the forceps or other device within the sheath is deployed behind the tip. Two embodiments are depicted in FIGS. 44 and 45. In FIG. 44, retrieval device 2765 includes an outer sheath 2766 and device tip 2767. The device is introduced into the patient via a guidewire 2771. Retrieval device 2765 includes a grasper or forceps 2768, a jacket or outer covering 2769, as discussed above, and a braided capture sleeve 2770, such as a capture sleeve made from Nitinol mesh. Retrieval device 2765 also includes X-ray or echogenic markers 2774 in useful locations, such as at the distal end of the outer sheath 2766 or the dilator 2767.

In use, the device tip is deployed when the user pushes the forceps 2768 distally, or withdraws the outer sheath 2766 in a proximal direction. The device tip is constrained to move axially along the guidewire 2771, and its location will thus remain in the control of the medical professional deploying or retrieving the prosthesis.

The embodiment of FIG. 44 features a device tip with a rather long transition section. When the user has advanced the retrieval device to the desired location within the patient, the sheath is withdrawn in a proximal direction, or the forceps is advanced in a distal direction to deploy the forceps and the basket. Because the device tip has a very gradual transition, the movement and the disruption to the patient are minimal. In this embodiment, the angle A of the device tip may range from about 10 degrees to about 30 degrees. Other angles may be used. The length of the transition section may vary from about 15 mm to about 25 mm. Other lengths may be used.

Another embodiment is depicted in FIG. 45. In this embodiment, the retrieval device 2775 also has an outer sheath 2776 and a separable device tip 2777. As shown in this view, the angle of the device tip is much greater than the previous embodiment, while the length of the device tip is much shorter. Retrieval device 2775 includes an inner sheath 2781 and a balloon 2782 and an inflation/deflation lumen 2783. Retrieval device 2775 also includes X-ray or echogenic markers 2779 in useful locations, such as at the distal end of the outer sheath 2776 or the dilator 2777. The length of the transition section may vary from about 5 mm to about 120 mm. Other lengths may be used.

In this embodiment, the retrieval device is used with the device tip and the internal balloon that is inflated to create a space for the retrieval device. In this embodiment, the retrieval device 2775 does not include a retrieval forceps at the outset. After the device tip is deployed and the balloon is expanded to create a space, the balloon is deflated and retracted and a retrieval forceps and basket are exchanged along the guidewire for the balloon and the inflation equipment. The balloon may be expanded by inflating the balloon to a pressure from 6 atm to 20 atm.

Designs for Retrievability and Redeployability

FIGS. 46-49 depict additional embodiments of interatrial implantable prostheses which have been designed for easier retrieval and also for redeployment once they have been retrieved. A first improved embodiment 100 a is depicted in FIGS. 46A-46B. The drawings depict several views of body element 100 a, showing how the ends of flange segments 102 a-102 h, 103 a-103 h are rounded at their distal ends 115 and 116 to reduce stress concentrations against the interatrial septum after placement. These distal ends, or apices where the strut legs intersect, include bores 109 a, 109 b, 110 a, 100 b into which radiopaque or echogenic markers 118 a, 118 b and 119 a, 119 b can be positioned. Using these markers, the device may more easily be visualized using radiographic imaging equipment such as with x-ray, fluoroscopy, magnetic resonance, ultrasound or other imaging techniques. Markers as disclosed herein may be applied to the ends of any segments, not just those with holes or eyelets therein. Radiopaque or echogenic markers 118 a, 118 b, 119 a, 119 b can be swaged, riveted, adhered, or otherwise placed and secured into the bores and dimensioned to be flush with the contours of the segments. As noted previously, suture rings 117 a, 117 b may be used to secure the left atrium flange segments 103 a-h to the right atrium flange segments 102 a-h.

The retrieval legs described herein may be made from nitinol wire, stainless steel wire (such as grades 304, 304L, 316 and 316L, among others), nylon sutures (e.g., polyamide), polypropylene sutures (e.g., Prolene®), or any other material that is medically acceptable and resistant to stretching. Materials that assume a known shape are desirable, as are materials that are visible under echographic or x-ray imaging conditions. The legs may thus take on a filamentary, thread, suture or wire shape, and may comprise a single thread or wire, or more than one suture, filament or wire. Wires made from nitinol or other metals may have a thickness from about 0.004 to 0.025 inches (about 0.11 to 0.64 mm). Sutures may range from about 8-0 to 7 (U.S.P. designations), i.e., from about 18 to 40 AWG, or even a little thinner than 40 gauge. The diameters of such sutures will range from about 0.04 mm to about 0.8 mm, and may apply to collagenous materials, synthetic absorbable materials, and synthetic non-absorbable materials.

FIG. 46A depicts several retrieval legs 135 joined to a central nub 137. The retrieval legs may be made of nitinol wires or of sutures and may extend from the bores 109 of right atrium flange legs 102 a-h to a central juncture or nub 137. Portions of the sutures or wires may be made from radiopaque materials or MR-visible materials so that the nub 137 is visible using non-invasive imaging techniques. At a juncture, the retrieval legs may be joined into a short tube 175 and crimped into tube 175. A single suture or wire loop 177, or more than one loop, may then extend above the crimp for joining to the inner catheter control wire, or for grasping by a retrieval device. A typical crimp tube is visible under x-ray or echographic (sound) imaging. Thus, the tube may be stainless steel or radiopaque plastic. One embodiment of the tube has a 0.035 inch i.d. (0.90 mm), 0.008 in (about 0.2 mm) wall thickness, and about a 0.050 inch (1.3 mm) o.d. Other embodiments may be used.

Retrieval loop 177 may be radiopaque or echograpically visible, or may include one or more threads that are radiopaque or echo-visible, such as a gold or platinum thread. The retrieval legs of this design do not interfere with the function of the prosthesis but do extend a short distance proximally, as shown in FIG. 46B. Thus, a filter, such as a thrombus filter, may be used as part of the prosthesis. In addition, the flow control elements described above may be used in the central portion of the prosthesis. These include the bivalve of FIG. 26, or a tri-lobal valve, or other embodiments, such as those discussed above with respect to FIGS. 29A-29C.

The prosthesis of FIGS. 46A-46B may be deployed from a catheter, as described above, and is retrieved in a similar manner, described below. The retrieval device secures suture or wire 177 from the central tube or crimp 175 with an appropriate end-effector, hook or grasper on its inner control wire. The inner wire of the retrieval device is then withdrawn proximally, drawing the sutures or wires into a catheter, collapsing the right atrium flange, and then drawing the remainder of the prosthesis into the catheter. The device may then be withdrawn from the patient, or may also be redeployed, perhaps in a better position.

A second design specifically for retrievability is depicted in FIGS. 47A-47B. Prosthesis 141 is similar to prosthesis 100 a of FIGS. 46A-46B. FIG. 47A is a top view, depicting prosthesis 141 with retrieval wires or sutures 143 connected to the apices 102 a-h of the right atrium flange. In this embodiment, there are two central nubs or points 145, each for about 180 degrees of the flange. The retrieval wires 143 are tied together to form a nub 145 on each side of the right atrium flange. As seen in FIG. 47B, the nubs 145 are then joined with a crimp tube 175, with a loop 147 of one or more retrieval wires or sutures joining the two crimp tubes 175 and sides of the prosthesis for removal. The retrieval wires or sutures, and the nubs, may be made from the materials described above. As depicted in FIG. 47B, the wires or sutures avoid the central area of the prosthesis when deployed from catheter 173 and thus do not interfere with the functioning or deployment of the valve. The wires or sutures are available to assist in withdrawal and removal or redeployment of the prosthesis if needed. Retrieval loop 147 may be radiopaque or echographically visible, or may include one or more threads that are radiopaque or echo-visible, such as a gold or platinum thread.

A third embodiment of a design for retrieval is depicted in FIGS. 48A and 48B. In this embodiment, prosthesis 151 is very similar to prosthesis 141 above, including retrieval sutures or wires 153 from bores 109 of the right atrium flange apices 102 a-h, to a central annular retrieval suture or wire 157. Each retrieval suture or wire 153 is joined to the central retrieval thread 157 at a juncture 155. The junctures may simply be suture tie-offs; alternatively, the junctures could be orifices in central wire 157 for joining retrieval sutures or wires 153. In some embodiments, an additional retrieval suture or wire 147, suitable for non-invasive imaging, may be tied to the central thread at least at one point for grasping by a retrieval device.

A fourth embodiment of a prosthesis 161 designed for retrieval and redeployment is depicted in FIG. 49. Prosthesis 161 is similar to prosthesis 100 a, described above. In the fourth embodiment, there is a retrieval wire or suture 163 secured to each apex 102 a-h of the right atrium flange and there is a retrieval wire or suture 167 secured to each apex 103 a-h of the left atrium flange. The right atrium flange retrieval wires or sutures are joined to a central point or nub 165 and secured to an inner control wire 171 b of a catheter 173. Central nub 165 may be a crimp tube and retrieval suture or wire, as described above. The left atrium flange retrieval wires or sutures are also joined to a central nub 169 and secured to an inner control wire 171 a. Central nub 169 may be a crimp tube and retrieval suture or wire, as described above. To deploy the prosthesis 161, the medical professional positions the prosthesis in the correct position within the patient and then releases the left atrium flange, disengaging the inner control wire from nub 169, and also releases the right atrium flange, disengaging the inner control wire from nub 165.

If retrieval is desired, the grasper or retrieval device grasps or engages both nubs 165, 169, preferably separately, with inner control wires 171 a, 171 b, or with graspers attached to them, to collapse the respective flange and withdraw the prosthesis, as described below. In one embodiment, left atrium flange legs 103 a-h have a greater radius R at their root and may even approach the septum wall at an obtuse angle, i.e., as shown in FIG. 49. This larger radius will make it easier to collapse the legs and struts of the flange. Once the prosthesis is withdrawn, it may be redeployed to a better position within the patient. Prosthesis 161 is capable of having both its left and right atrium flanges collapsed. If separate control wires are used, one for each flange, the flanges may be collapsed separately in time, thus requiring less force to withdraw.

Stents for Providing Coronary Sinus Pressure Relief

Per the discussion on heart failure, and consistent with the present disclosure, it may be beneficial for some patients to relieve pressure in the left atrium. One way to accomplish this is to provide communication between the left atrium and the coronary sinus. The coronary sinus and its tributaries receive approximately eighty-five percent of coronary venous blood. The coronary sinus empties into the posterior of the right atrium, anterior and inferior to the fossa ovalis. A tributary of the coronary sinus is called the great cardiac vein, which courses parallel to the majority of the posterior mitral valve annulus, and is superior to the posterior mitral valve annulus.

Thus, by providing communication between the left atrium and the coronary sinus, inappropriate pressures in the left atrium can be averted, with the blood diverted to the most appropriate blood vessel possible, the coronary sinus. In cases of mitral valve failure or disease, it is possible that providing this communication could allow the patient to put off or forgo mitral valve repair. This could provide additional quality of life to the patient, while avoiding surgery that is more involved and more delicate.

Embodiments of the stent described herein may be placed via minimally-invasive surgery, such as through endoscopic or percutaneous (vascular access) routes, or by traditional surgical methods. Minimally invasive procedures are more easily tolerated by the patients, who may also recover much more quickly from the procedure. In embodiments where the device is implanted into the atrial wall via a minimally invasive procedure, a catheter may be used, as shown generally in FIG. 50. A catheter, such as an introducer catheter is introduced through a jugular vein or a subclavian vein, through the superior vena cava (SVC), along the path of arrows A, and into the coronary sinus CS of the heart H. It is also possible to place the catheter via a femoral vein, through the inferior vena cava (IVC), along the path of arrows B, and into the coronary sinus.

As is well known to those with skill in surgical arts, it is useful to first define the pathway via a guidewire, such as a 0.035 inch diameter (about 0.9 mm) guidewire or 0.038 inch dia. (about 1 mm) guidewire. Guidewires of other diameters may be used as needed or desired. The catheters may be maneuvered to their locations by carefully following the appropriate guidewire. It is also well known to those with skill in surgical arts that other pathways for the catheter may be used, such as through the pulmonary veins, or even through arterial pathways. If patient anatomy suffices, however, the easier method is to go through the route of the SVC as discussed above.

FIG. 51 depicts one method of deploying the stents described herein. In FIG. 51, a guide wire 10 is introduced through the jugular vein (not shown), through the superior vena cava and into the coronary sinus. Once the wire guide provides a path, an introducer sheath 12 may be routed down the guide wire and into position in the coronary sinus. The introducer sheath or introducer catheter is used to provide vascular access. The introducer sheath may be a 16 F or less hemostasis introducer sheath. Alternatively, the subclavian vein may be used. In one embodiment, introducer sheath 12 may be about 30 cm long. The guidewire may be somewhat longer for ease of use. In some embodiments, the introducer catheter may also function only as a dilator and an assistant for preparing an opening in the wall of the left atrium. In these embodiments, a separate placement catheter will be used. In other embodiments, the introducer catheter may be used as the placement catheter also.

Since the coronary sinus is largely contiguous with the left atrium, there are a variety of possible acceptable placements for the stent. The site selected for placement of the stent, may be made in an area where the tissue of the particular patient is less thick or less dense, as determined beforehand by non-invasive diagnostic means, such as a CT scan or radiographic technique, such as fluoroscopy or intravascular coronary echo (IVUS).

In FIG. 52, a bending catheter 16 is depicted, guide wire 10 is still in place but is not shown for clarity. In one embodiment, bending catheter 16 may be about 145 cm long. A closer look at the introducer catheter 12 and the bending catheter 16 is depicted in FIG. 53. The introducer catheter 12, equipped with a peripheral opening 13 and at least one marker 14 for radiographic or echogenic location, is shown within the coronary sinus. As noted, the wire guide 10 is still in place. In one embodiment, bending catheter 16 is about 145 cm long and has a very flexible or floppy tip 18 for precisely positioning the catheter. In one embodiment, the tip 18 is capable of a 90° bend so that the medical professional has very close control of its location and can easily use the catheter in the desired location. Bending catheter 16 is also equipped with one or more echogenic or radiographic markers 14 near the tip so its location may be discerned by non-invasive means, such as fluoroscopy or ultrasound techniques. Catheters with very flexible, e.g., floppy 90° distal tips, are available from Baylis Medical Company, Inc., Montreal, Canada.

As further shown in FIG. 54, once the bending catheter 16 and very flexible tip 18 are in the proper position, an RF wire 19 will be placed into position through catheter 16 and used to ablate the tissue and to penetrate the wall between the left atrium and the coronary sinus, which is relatively delicate tissue. Care should be taken, however, that tissue remains integral with the wall and that no loose tissue is created when the opening is made.

For example, bipolar or monopolar radio-frequency (RF) energy may be applied to the desired area to ablate or vaporize tissues in the area to form an opening. Several techniques in this area of described in a co-pending provisional patent application assigned to the assignee of the present application and entitled “Interatrial Pressure Relief Shunt,” and filed on Feb. 10, 2011, U.S. Prov. Pat. Appl. 61/441,546, the contents of which are hereby incorporated entirely by reference and relied upon. Additional precautions may be taken in certain of these techniques, such as providing a grounding pad for the patient at least when using monopolar electrical equipment.

Piezoelectric ultrasound techniques and piezoelectric ultrasound sensors or sensor arrays in the desired abrading area, also discussed in the above-mentioned patent document, may instead be used. Typically, DC equipment is used for RF techniques and equipment while AC equipment is used for ultrasound or piezoelectric equipment. The area in the immediate vicinity where ablating is to take place may be protected by heat transfer equipment. For example, cooling coils may be delivered by suitable catheters and placed in the area, such as in an annular ring surrounding the electrodes or sensors that deliver the ablating energy. Cooling fluids, such as saline, may be pumped through the cooling coils to counteract the very hot temperatures generated by the ablating devices. Ablative equipment is available, for example, from Baylis Medical Company, Inc., Montreal, Canada.

In one embodiment, the opening made in the atrial wall by ablation may then be enlarged. The RF wire 19 with its flexible tip may be removed through sheath 16 and a balloon catheter 20, inserted, through sheath 16 as shown in FIG. 55. Balloon catheter 20 may also be equipped with markers 14. In this technique, balloon catheter 20 with tip 22 and with a balloon 24 is guided to the opening and the balloon is inserted into the opening between the coronary sinus and the left atrium. Using inflation lumen 26, the balloon is inflated and the opening enlarged to the desired diameter. When the opening has been made, the balloon may be deflated through deflation lumen 28 and then removed through the sheath 16. Alternatively, any suitable dilator may be used, such as a Mullins™ dilator with a needle or cutting edge or a conical distal tip of a dilator catheter. The method employed must be very reliable and very controllable by the medical professional in all stages of its deployment. The size of the opening desired may range up to about 8 mm, although smaller openings may also be suitable.

Once the opening is made between the left atrium and the coronary sinus, a deployment catheter 30 is used, as depicted in FIG. 56. Similar depictions are seen in FIGS. 8-11 above, in which the prosthesis is in a compact or folded state prior to deployment. The deployment catheter 30 may be used with a guide wire 10 only or it may be used with a sheath catheter 12, as seen above. In the figures that follow, a sheath catheter is not shown, for simplicity, but it may be used for ease of insertion and then withdrawn before deployment of the stent. The deployment catheter 30 includes an outer sheath 32 and an inner control wire 34. Outer sheath 32 may also include one or more radiographic or echogenic markers 36 so the sheath may be easily seen by non-invasive techniques and its location adjusted as need for proper placement.

Deployment catheter 30 also includes a stent 40 folded up within the catheter. As detailed below, stent 40 may be in generally in a shape of a T, with a longer portion and a shorter perpendicular section. The longer portion is intended for implantation in the coronary sinus, with the perpendicular portion extending into through atrium wall into the left atrium. The stent should extend through the atrium wall, but the extension into the left atrium should be minimal, for example, only 3-4 mm. This distance is believed to insure secure implantation without extending so far as to interfere with movement of the left atrium during normal heart operation.

Stent 40 is deployed using control wire 34, which extends backwards through catheter 30 to a control device or handle (not shown) accessible to a medical professional guiding the catheter. As is well known to those with skill in the art, the catheter is deployed by holding the control wire in place while gently withdrawing the outer sheath 32. As the sheath is withdrawn, the stent expands and deploys in place in the coronary sinus. As is also well known, stent 40 is prepared from medically acceptable prosthesis materials, such as Nitinol, stainless steel, MP35 or other materials. Nitinol or other shape-memory alloys allow manufacturers to prepare stents and train them to assume the desired shape once they are returned to body temperature and are deployed in the body. When freed of the restraints of the confining catheter, the stent will expand and assume the shape for which it was trained.

Stent 40 is depicted in its undeployed state in FIG. 56 and in its deployed state in FIG. 57. The deployed stent is in a general form of a tube, with longer portions 41, 42 intended for implantation in the coronary sinus and a shorter portion 43, intended to be perpendicular to longer portions 41, 42 and for extension through the orifice made in the wall of the left atrium. In the deployed state, the shorter top portion 43 is intended to protrude through the orifice. In the closer view of FIG. 57, it is seen that both portions of the stent has the appearance of about eight struts 44 joined at apices 45, as also shown in greater detail above in FIG. 2A. In some embodiments, the stents are not made of discrete struts but rather are laser cut or water jet cut from a thin, solid tube of nitinol or other desired material. Thus, the stents may better be described as a network, or mesh, of struts and intersections of struts. In one embodiment, at least the shorter portion 43, and also the longer portions 41, 42 include one or more markers 46 made of a radiopaque or echogenic material. In the closer view of FIG. 2A, note that the outer portions are smoothly rounded to avoid any trauma to the heart tissue, for example, with a radius of curvature greater than 0.03 inches (about 0.8 mm).

The stent thus implanted should be capable of two important tasks. The stent should be sized so that the longer part, portions 41, 42 remain in place within the coronary sinus without movement. Accordingly, the diameter of these portions should be in the range of about 8-13 mm, perhaps in the range of 8-11 mm, because the posterior portion of the coronary sinus, in the desired location, is a little smaller than the anterior portion. With the longer portion of the stent fixed in place, the shorter portion, or crown portion 43, will also remain in place.

Once placed, the crown also will not move and will be in a position to keep the orifice open between the left atrium and the coronary sinus. Accordingly, it should not be necessary for the upper portion to exert much force on the opening, and it will be desirable for this portion to be flexible and atraumatic rather than stiff. The coronary sinus is very sensitive to abrasion and the stent portions that reside in the coronary sinus need to be atraumatic while the LA legs need to conform to the curvage or the radius of the opening into the left artrium chamber. At the same time the transverse or crown portion of the stent needs to be strong enough to keep the freshly made opening between the coronary sinus and the left atrium from closing; this would defeat the purpose of the prosthesis. In other embodiments, described below, the upper portion may form a flange, with longer or shorter extensions along the longitudinal direction of the stent, as shown in FIGS. 58 and 59.

In FIG. 58, stent 50 includes a top portion or flange 51 with about 4 protruding triangular struts 53. The radius of curvature is relatively tight, from about 5 mm to 15 mm, so that the flange is not held tightly by the atrial wall in the vicinity of the flange. The flange in this embodiment extends about 2-4 mm in a direction parallel to the coronary sinus. In FIG. 59, stent 56 includes a top portion or flange 57 with about 6 (not all are shown) protruding struts 58. The radius of curvature 59 here is somewhat looser, from about 10 mm to about 40 mm. In one embodiment, the flange extends only about 1-2 mm in a direction parallel to the coronary sinus. Like the annular flange described in connection with intra-atrial stents/devices above, the flange 51 may be annular and comprise a plurality of flange segments in all the same configurations as mentioned above in connection with the intra-atrial stent, including varying flexibility of the flange or flange segments. For example, the flange and/or flange segments may be more flexible than the transverse portion of the stent to achieve the atraumatic contact discussed in the preceding paragraph.

One aspect of the stents for enabling communication between the left atrium and the coronary sinus is that it may be desirable to have only one-way communication. One embodiment of the stent is designed to allow pressure relief of the left atrium by providing an outlet to the coronary sinus without allowing retrograde flow. The coronary sinus directs blood flow from several veins, such as the small, middle, great and oblique cardiac veins, the left marginal vein and the left posterior ventricular vein. It is not desirable, however, to allow flow from the coronary sinus into the left atrium. The stent may thus be restricted to one-way flow by providing the stent with a flow control element of the type disclosed elsewhere herein.

FIGS. 60 and 61 depict two embodiments of a stent limited to one way communication by a restricting valve. In FIG. 60, stent 60 includes a top portion 61 intended for deployment above the wall between the left atrium and the coronary sinus. Stent 60 also includes a transverse portion 67 intended for deployment within the coronary sinus as described above. Top portion 61 in this embodiment includes a multi-part flap valve 63 secured to the top portion 62 of tower 61 with sutures 64. While the flap valve 63 in this embodiment has two portions a bi-valve, that meet roughly along a diameter of the top portion, other embodiments may have three or more portions, again, meeting in the middle. It is also possible to have a single flap, tethered perhaps along one side by about 30-45 degrees of the circumference. This embodiment also includes one or more stops 65 to prevent the valve from opening in the other direction and allowing blood to flow from the coronary sinus into the left atrium. The flow control element could also be a ball and socket valve, a duckbill valve, a butterfly valve, or any other valve component known to those skilled in the art or as those disclosed in the commonly-owned application mentioned above.

As is well known to those with skill in cardiac arts, the valve or flap may be made of mammalian pericardium, such as bovine pericardial tissue, or from ovine or porcine pericardial tissue. Other suitable tissue may also be used. In one embodiment, the tissue is about 0.5 to about 1 mm thick. Other thicknesses may be used. The valve and the flaps are designed so that blood will flow through the one-way valve when the pressure differential reaches about 5-10 mm Hg. Any of the valves/materials disclosed above in connection with intra-atrial stent may also be used.

FIG. 61 depicts another embodiment of a one-way valve useful in the stents disclosed herein. In this exploded view, valve 70 is formed within the top portion 71 of a coronary sinus pressure relieving stent. The valve includes a plate 75 with multiple perforations 76. While perforations 76 are shown as slots, they may be made of any suitable shape. The plate itself made may be made of any material suitable for in vivo contact with blood, including inert polymers such as polycarbonate or polysulfone, or metals such as stainless steels, MP35N or Nitinol. As shown, perforated plate 75 is adjacent the distal end of the stent top portion 71. On the opposite side of the perforated plate 75 is a valve element 73 with flaps 74. In one embodiment, flaps 74 are slightly larger that the gaps beneath the flaps, enabling the flaps to seal tightly if for some reason the pressure in the coronary sinus exceeds the pressure in the left atrium, on the far side of the stent.

During normal operation, when the pressure in the left atrium exceeds the pressure in the coronary sinus, blood will tend to flow from the left atrium through the stent, and in particular at the outset, through the top portion 70. Blood will flow through the perforated plate 75 and since the flaps 74 are free to flap downward, in the embodiment of FIG. 61, the blood will flow through valve element 73 and on into the coronary sinus. However, the flaps 74 are not free to flow in the opposite direction, toward the left atrium, because their movement is prevented by the perforated plate 75. Other embodiments of check valves or one-way valves may also be used.

Other embodiments of stents for relieving pressure may have other configurations. For example, FIG. 62A depicts a T-tube stent in a before-deployment configuration. Stent 80 includes a longer portion 81 in a general shape of a cylinder for placement in a coronary sinus of a patient. The stent is constructed of short struts 84 and apices 86 joining the struts, or as mentioned above, an interconnecting network of struts and joining areas. A shorter portion, tower 82 is folded within the longer portion 81. Upon deployment of the stent within a patient, the longer portion will expand if the stent has been trained to do so when the austenitic transition occurs upon warming to body temperature. The tower portion 82 may then be deployed from its retracted position within the longer portion to its deployed position, as shown in FIG. 62B.

The tower will assume its intended shape as it is deployed and as it warms to body temperature. The tower includes a wider portion, i.e., a portion with a larger diameter that will reside within the left atrium. The tower also includes a narrower portion 83 having a diameter about the diameter of the opening which was prepared for the stent. Tower portion 82 may be pushed into place, for example, by a balloon catheter if it fails to deploy properly by the “memory metal” effect. While the principal portion of the stent is constructed of struts and apices, in this embodiment, the tower may be made from many more flexible, thinner wires 88 for greater ease of deployment. In one embodiment, the wires are 0.003 in (0.08 mm) diameter and are thus very flexible. The wires form a porous closed “net” whose openings allow blood to flow from the left atrium to the coronary sinus.

Device Control

Heart disease has many causes and many factors to consider when determining a treatment plan. Detection of conditions that indicate a critical potential for heart related problem may facilitate quick and effective treatment. Based on the conditions that are detected, combination treatment may provide greatly improved response and may be highly beneficial to the recovery or stabilization of a patient's health condition. While an intra-atrial shunt or atrial pressure regulating (stabilizing) device can be an important solution to some heart disease-related problems, combining other treatments with such a shunt may significantly benefit a patient. Also, due to the invasive nature of shunt implantation, combining such a shunt with other monitoring and sensing technology can increase the value of such an implantation.

Combined therapy that incorporates a shunt, responsive drug administration, internal physiological parameter sensing, remote monitoring and control can also facilitate improved treatment of patients with severe heart conditions or disease while enabling such patients to live more normal lives.

Advances in medical device technology also make it reasonable to consider combining various therapeutic, sensing, control and treatment capabilities into a single multi-function implantable device.

To facilitate such improvements in treatment we describe herein combining shunts, sensors, drug treatment systems, and the like in various ways with new sensing techniques, sensing technologies, sensed condition analysis, materials advances, and the like.

The present disclosure may provide a means for controlling operation of a valve of a device implanted in a subject's heart thereby controlling the flow through the device. Flow in one or both directions may be controlled. Because too much flow back into a right atrium may damage the right atrium over time, it may be necessary to control the flow in one direction through the device differently than in the opposite direction. In an example flow in a first direction may be restricted while leaving unchanged or even increasing the flow in a second direction. Thus, the present disclosure may include a device control facility which may control the pressure on either side of the device and may control in a variety of ways the blood flow through the valve of the device.

Referring to FIG. 63, a schematic embodiment of sensing and control features of device 400 is depicted. Note that detailed embodiments of the device are described herein and each embodiment shall be understood to apply to the description of an inter-atrial pressure regulating device herein. A device control facility 410 may comprise a processor 412, such as a microprocessor, a microcontroller, and the like capable of controlling aspects and components of the device control facility 410. The device control facility 410 may further comprise a power source 414, data storage 416, a communication facility 418, an internal sensor 420, an external sensor 422 and a valve adjustment motor or actuator 424.

The power source 414 may be internal to the device control facility 410 or may be external and connected to the facility 410 such as by a power wire, cable, or the like. The power source 414 may be any type of small battery, electrical energy storage device, power conversion device (e.g. that converts biological processes to electricity), and the like. The power source 414 may be rechargeable, such as through a wireless transmission of power, or other type of wireless energy. With reference to the devices described above in FIGS. 2-3, 18-19, 24-26 and 30, the external sensor 422 may be mounted to any portion of an atrial septum prosthesis, including, for example, a flange segment, the first annular flange or the said second annular flange, or the core segment.

Small motors or actuators have been developed with the capabilities of moving the flaps or adjusting the orifices of the valves depicted above in FIGS. 24-26 and 29A, 29B and 29C. The motors or actuators may be piezo devices, which move when electricity is applied to a portion of the motor or actuator. The motor or actuator may be mounted on the implantable device 400, which may be anchored to the atrial wall of the patient. The movable portion of the motor or actuator is then anchored to a movable flap or portion of the valve, such as the tricuspid valves, bicuspid valves, single flap valves or other valves discussed above. These may include duckbill valves, leaflet valves, flap valves, or any other small valves. The characteristic of these valves is that flow of blood through the atrial opening may be altered, stopped or substantially stopped by movement of one or more flaps, and then resumed by movement of the one or more flaps.

Such motors or actuators are available from a variety of sources, including New Scale Technologies, Victor, N.Y., USA, and Physik Instrumente LP, Auburn Mass. and Karlsruhe, Germany. These motors are described, for example, in Piezo Motors and Actuators: Streamlining medical device performance, DesignFax News, Mar. 23, 2010, (5 pages) which is hereby incorporated by reference in its entirety. See also Low Power Piezo Motion, DesignNews, May 5, 2010 (4 pages), and Piezo for Motion Control in Medical Design and Drug Research, from Physik Instrumente. Brochure, Nov. 21, 2010 (22 pages) which are also incorporated by reference in their entirety. A number of applications are also described in Medical Design Technology (magazine), April 2009, in the 12-page article entitled, Piezo Motor Based Medical Devices, which is hereby incorporated by reference in its entirety.

Small implantable sensors have been developed and are available from a variety of sources. Examples include tiny pressure sensors available from Fraunhofer Gesellschaft, Munich, Germany. Other implantable pressure sensors include the Chronicle IHM (implantable hemodynamic monitor) series, available from Medtronic, Inc., Minneapolis, Minn., U.S.A. See also Implantable Sensors for Heart Failure, Faisal M. Merchant et al., Advances in Arrhythmia and Electrophysiology, Circ. Arrhythm. Electrophysiol., 2010:3:657-667 (2010), which is hereby incorporated by reference in its entirety. New sensors are being developed continually, such as new implantable wireless-communicating sensors from Renssalear Polytechnic Institute (RPI), Troy, N.Y., U.S.A. See Implantable, Wireless Sensors Share Secrets of Healing Tissues, RPI Newswise, Feb. 21, 2012, which is hereby incorporated by reference in its entirety. These are examples of cardiac implantable electronic devices (CIEDs) which are helping to revolutionize medical care.

In embodiments, the power supply 414 may provide power that is sufficient to enable all components of the device control facility 410 and the valve adjustment motor 424 to function properly under a range of environmental and mechanical conditions as may be exhibited by the subject in which the regulating device 400 is disposed. An internal sensor 420, external sensor 422, or a combination thereof may produce a reading of a parameter measured in the heart for example a parameter indicative of blood pressure or flow (e.g. in proximity to the device 400), such as for feedback to the processor 412 to control the operation of the valve. The pressure or flow reading may be sent to the processor 412 which may store it in the data storage 416 along with a time stamp indicative of the time that the reading was sensed, which can be later output by an output device including any external device or monitoring device described herein. A plurality of such pressure and flow readings may be stored in data storage 416 to facilitate creating a plot, graph, report, and the like of pressure and flow readings over a period of time, which may be displayed or otherwise communicated by an output device described herein. The processor 412 may also store data that is indicative of valve adjustment motor 424 control operations. This valve adjustment motor 424 control operation data may be stored in combination with time stamps to facilitate combining with the pressure or flow reading data to facilitate creating a correlation between the adjustment of the valve within the device 400 and the pressure or flow.

The valve adjustment motor 424 control operation data may include motor settings, valve settings, setting offsets, adjustment rates, and other data as may be available to the processor 412 (e.g. other sensor data, date and time data, and the like). The processor 412 may route any of the stored data to the communication facility 418 to be delivered to a monitoring device. The communication facility 418 may communicate with a monitoring device (not shown), such as an external monitoring device via a wire or wirelessly. The communication facility 418 may include a portion that is distal from the device 400 but that otherwise facilitates a wired connection. Such an embodiment of the communication facility 418 may include a port that is accessible at the skin of a subject for connecting to a monitoring device through a wired connection. In an example of controlling the valve, the processor 412 may execute instructions based on parameters sensed by the sensors to send a signal to the valve adjustment motor 424 which may cause the valve inside the device 400 to be manipulated so that the pressure or flow through the valve is changed. The signal sent to the valve adjustment motor 424 may include a variable voltage signal, a variable frequency signal, a variable current signal, a direct current (DC) signal, an alternating current (AC) signal, a pulse (e.g. positive or negative voltage), and the like that may be received by and interpreted by the valve adjustment motor 424 to control the operation of the valve.

As shown in the embodiment of FIG. 63, the device control facility 410 may be located remotely from the device 400. In this embodiment, the valve adjusting motor or actuator 424 may be attached to, embodied within, and/or located in proximity to the device 400 to enable it to control the valve. The connections among the device control facility 410, the device 400, and the valve adjustment motor 424 may be wired, wireless, or a combination thereof.

An example of a piezo actuator and a flap valve is depicted in FIG. 64. In this example, a piezo actuator or motor 450 includes a stationary portion 452 that is mounted to a prosthesis or device implanted near the atrial wall. Such a device may include any of the devices mentioned above. The motor or actuator also includes a movable portion 454 that moves when electricity is applied between the stationary portion and the movable portion. A flap 458 is mounted to the mounting portion 456 of the actuator 450. When flap 458 is in an upper position, which may be the at-rest position, blood flow is allowed in an opening of the atrial wall between the left atrium and the right atrium. When the user or a physician feels that the opening should be restricted, the piezo motor or actuator 450 may be used to lower the flap 458 to restrict flow or to close the opening. The flap 458 closes against the lower portion 400 a of a shunt or other device used to allow or restrict flow through the atrial wall.

Referring to FIG. 65, the device control facility 410 may be disposed within, or integrated with the device 400 itself. Such a disposition may allow for easier insertion and removal of the two devices, and may allow for better communication between the two devices.

The device control facility 410 may be enclosed in a housing that may be adapted to be disposed in contact with human-like tissue and bodily fluids, such as blood so that, for example, the control facility 410 may be disposed within the intra-atrial region of a heart or elsewhere in the body of the subject.

As described herein above, the processor 412 may send a signal to the valve adjustment motor 424 that may cause the motor 424 to manipulate the valve. The valve adjustment motor 424 may open (fully or partially) or close (fully or partially) the valve as signaled by the processor 412. The valve adjustment motor 424 may adjust the valve so as to restrict flow through the valve to a Qp/Qs value of 1.5. The valve adjustment motor 424 may manipulate the valve apertures or leaflets, as the case may be, which may facilitate regulating pressure and flow associated with the intra-atrial operation of the heart. Further, the valve adjustment motor 424 may change the shape of the valve which may also regulate pressure and flow. As an example, and not a limitation of the shape change functionality, the valve adjustment motor 424 may close blades to constrict the barrel of the valve, contract the barrel of the valve, expand to take up space within the barrel of the valve, and the like.

In embodiments, the device control facility 410 may facilitate the creation of an alert or notification, which can be outputted by any of the output devices described herein. An alert may be generated be based on a sensed parameter, such as a pressure or flow reading which is outside a desired range, the presence of a certain characteristic such as a chemical, and the like. The device control facility 410 may receive a sensed parameter from an internal sensor 420 or an external sensor 422 and may use the communication facility 418 to send an alert to an external monitoring device. The external device may be an implantable medical device, such as a pacemaker, a therapy delivery device, and the like. The external device may also comprise remote equipment, such as a monitoring device (for example, a heart monitor), a computing device (e.g. mobile phone, PDA, pager, or the like) used to alert a patient, physician, or nurse, and the like. The external device may be programmed to automatically react to an alert from the device control facility 410. In an example, a pacemaker may change its timing, a medicine delivery system may release more medicine, and the like based on the receipt of an alert. The device control facility 410 may generate a variety of alerts that may indicate different conditions that may require a different reaction from the external equipment. The external device may also produce an audible, vibratory, or visual signal in response to receiving an alert.

Further in the embodiment, the ability to create an alert or notification may facilitate monitoring a parameter associated with the operation of the device 400. Upon detection of an alert condition, data for the monitored parameter (and/or other data that may be pertinent to the alert condition) may be sent to a monitoring or diagnostic system by the device control facility 410. A plurality of such parameter data values may be stored by the monitoring system for recall by a physician or a nurse to help fine-tune operation of the device 400 to enhance therapy related thereto, or to administer a separate treatment of the patient. In an example, a physician may analyze the data stored by the monitoring system and may notice in the data a particular abnormality that occurs with a particular pattern of other data values (e.g. based on time of day) and may adjust the pressure and flow of the valve ahead of the abnormality's next occurrence. The physician may adjust a set of valve control settings in the external monitoring system that may communicate the adjusted set of valve control setting to the device control facility 410 for use by the processor during control of the valve.

In embodiments, the device control facility 410 may establish a sense-and-control loop for monitoring and manipulating the valve. The control loop may be automated, requiring no outside interaction. The internal sensor 420 and/or external sensor 422 may monitor blood pressure and flow proximal to the device 400. The processor 412 may process a pressure and flow reading from a sensor. The processor 412 may compare the pressure and flow reading against an accepted range and may send a signal to the valve adjustment motor 424 to adjust the value thereby regulating or manipulating pressure and flow through the device 400 if the reading is outside a desired range. Further in the embodiment, the processor 412 may periodically poll the internal sensor 420 or the external sensor 422 for a current pressure and flow reading, recording each reading within the data storage 416. Additionally, the processor 412 may record movement by the valve adjustment motor 424 that manipulates the valve to impact the pressure and/or flow rate.

The processor 412 may be programmed to evaluate one or more pressure and flow readings taken by one or more internal sensors 420 or one or more external sensors 422 and recorded over a period of time (e.g. a day, week, month, and the like). The processor 412 may capture and record readings from the sensors described herein, such as a pressure and flow reading taken immediately before and immediately after sending a valve control signal to the valve adjustment motor 424 to facilitate calculating the effect of the valve adjustment. Thus, the processor 412 may continuously monitor pressure and flow through the valve and the effect of any adjustments in order to fine-tune valve adjustment.

In another embodiment, the control loop may be manual (e.g. during an initial setup or therapeutic adjustment process), and may require interaction with an external device, a physician, a nurse, and the like. The communication facility 418 may send a current pressure and flow reading to an external device being monitored by a physician who may manually change the pressure and flow setting by manipulating valve control settings in a user interface of the external device that may be communicated to the processor 412, creating a manual control loop.

In embodiments, the device control facility 410 may comprise a servo which may be used to establish a closed loop between a sensor and a range of desire performance. The closed loop may allow the device control facility to make on the fly adjustments of pressure and flow through the valve.

Delivering Therapy

The present disclosure may provide a means for delivering a therapy in combination with implantable devices described herein. The therapy may comprise a medicine or the administration of therapy via an electrophysiological device. A medicine may be one of a diuretic, an antihypertensive, an anticoagulant, and the like. An electrophysiological device may be an atrial defibrillator, a left atrial pacemaker, and the like. The therapy may be delivered by a therapeutic delivery mechanism located within the device. The device may also comprise a sensor and a controller. The controller may be in communication with the sensor and the therapeutic delivery mechanism and may be configured to actuate the therapeutic delivery mechanism.

In embodiments, a sensor within the device may generate a parameter indicative of pressure, flow, electrical conductivity, chemistry, electrolytes, respiration rate, oxygen saturation, and the like. The sensor may be one of a chemical, mechanical, electrical, piezo-electrical, Doppler, ultra sound, and the like. The sensor may generate a parameter of a heart, a right atrium, a left atrium, blood in the heart, and the like. The sensor may generate the data indicative of a parameter continuously, creating a data stream. The device may comprise a plurality of sensors which generate data on a plurality of parameters, which can then be transmitted for further processing.

Sensors may be used in conjunction with the device 400 to detect and react to a variety of conditions including, flow, turbulence, changes in flow, flow direction, flow velocity, atrial pressure, biological factors, chemical factors, electrical factors, electrolytes, blood oxygen level, respiration rate, detection of other therapies, and the like. The location of the device may facilitate proximate assessment of electrolyte levels and biomarkers of cardiac myocyte damage (troponin) or heart failure severity (BNP). Any of the sensed conditions or parameters described in this disclosure may be utilized with any of the various embodiments having a sensors and/or a therapeutic administration facility to report information related to the sensed parameter(s) or to adjust the operation of the therapeutic administration facility based on the sensed parameter(s).

In embodiments, the device 400 may be associated with chemistry sensors, and in some embodiments may include chemistry sensing capabilities. Chemistry sensors may detect a physiological change such as a change in a concentration of a cytokine, a metabolite, a cardiac enzyme, and the like, and may be indicative of a lymph node condition.

In an example, an implantable chemistry sensor may provide a sensor signal representative of metabolites, such as lysophoglycerides (LPC) and cardiac enzymes like troponins in the lymph node fluid, to the device control facility 410 of the device 400. Other types of chemistry sensors associated with or used in combination therapy with the device 400 may detect level changes of B-type natriuretic peptide (BNP) in the blood to facilitate diagnosis of heart failure. The BNP may be used as a biomarker in assessing cardiovascular diseases. Yet other types of the implantable chemical sensors may provide a signal representative of blood pH, blood electrolytes such as one or more level of potassium (K), sodium (Na), calcium (Ca), glucose, or creatinine. In yet another sensor use scenario, the chemistry sensors may be used in conjunction with the device 400 to detect various conditions such as atrial pressure, blood oxygen level, and the like.

Implanting the device 400 may impact hemodynamic monitoring due to the pressure equalizing abilities of the device 400 by facilitating blood flow between the LA and the RA. Techniques such as closing a valve of the device 400 for independent LA and RA hemodynamic monitoring, adapting a catheter that may work in association with the device 400 to allow the adapted catheter to pass through the device 400 opening to measure a pressure on the LA or RA. The catheter may operate with the device to temporarily close the valve of the device 400, such as to get hemodynamic information from the left atrium by inserting the catheter from the right atrium. The hemodynamic information may include pressure measurements, blood flow, and blood oxygen saturation measurements.

Further in the embodiment, a controller may communicate with a sensor. The controller may actuate a therapeutic delivery mechanism to deliver a therapy based on a parameter reported by a sensor. The controller may process a parameter reported by a sensor or may process the data stream generated by a sensor. In embodiments, the controller may combine a parameter reported by one sensor with one or more parameters reported by one or more other sensors. The controller may regulate the delivery of a therapy based on one or more parameters reported by one or more sensors.

Many individuals with diastolic dysfunction suffer acute increases in systemic blood pressure that are often associated with rapid rises in left atrial and pulmonary pressures. Though there is no clear consensus as to why diastolic heart failure patients experience these systemic hypertensive spikes, it is broadly believed that these spikes directly cause an increase in left atrial pressure. The left atrial hypertension in turn, leads to the systems of heart failure that ultimately cause patients to be breathless and require hospital admission. More broadly, in addition to being a problem in diastolic heart failure, hypertension is known to exacerbate other forms of heart failure as well.

In embodiments, an antihypertensive may be used in conjunction with the device to help prevent a hypertensive crisis or to manage a left atrial hypertension if a hypertensive crisis occurs. The antihypertensive may be one of a beta blocker, a calcium channel blocker, a remodeling agent (such as an ACE inhibitor, an angiotensin receptor blocker, a rennin inhibitor, or an aldosterone receptor antagonist), and the like.

As many as 30% percent of patients with diastolic heart failure have concomitant atrial fibrillation. Many more may have clinically silent atrial fibrillation. The treatment of atrial fibrillation often necessitates anticoagulation to prevent systemic thromboembolization. In embodiments, an anticoagulant may be used in conjunction with the device to prevent embolization and allow left atrial decompression. The combination of an anticoagulant with a device may reduce the significant risk of a diastolic dysfunction during atrial fibrillation.

In embodiments, the device may comprise an atrial defibrillator for delivering electrical pulses or impulses (shocks) to a patient's heart. A sensor within the device may monitor the atrial rhythm while the device provides left atrial decompression. The atrial defibrillator may deliver a voltage to shock the atrium into a sinus rhythm when atrial fibrillation is reported by the sensor.

In embodiments, the device may comprise a left atrial pacemaker. The left atrial pacemaker may provide a more synchronous A-V electrical conduction pattern and may maintain a sinus rhythm by properly pacing the left atrial while the device provides left atrial decompression. In embodiments, a pacemaker signal may be amplified. A sensor may sense that the pacemaker signal dissipates as it goes over a fibrotic and enlarged atrium. The device may amplify the pacemaker signal by using a pulse generator, a battery, and the like. In embodiments, the amplifier may include a micro-electro-mechanical system (MEMS) based axial flux power generator. The MEMS generator may function due to the physiological motion of the body organs to induce voltage across an underlying copper coil. The MEMS generator may provide a greater energy supply per unit volume as compared to the existing pacemaker batteries and its use may also facilitate developing smaller pacemakers. In another embodiment, the MEMS generator may be configured to provide early detection of a formation or presence of an occlusion within a body fluid vessel such as an artery.

In embodiments, the present disclosure may be used as a shunt within a surgically created baffle. In several types of congenital heart disease in which babies are born cyanotic and venous blood does not have the opportunity to be oxygenated before returning to the general circulation, surgical baffles are often created to redirect blood within the heart and lungs. A device may be used as a shunt to alleviate a pressure build up within a surgically created baffle. In an example, this arrangement may allow R to L shunting in patients with a failed Fontan procedure in whom the pressure within the baffle exceeds a certain threshold limit.

In embodiments, a sensor with the device may observe and report both left and right atrial pressure, flow, volume, and the like. The sensor may communicate with the controller which may calculate the appropriate dosage of therapy to be dispensed by the therapeutic delivery mechanism.

In embodiments loop diuretic titration may be based on a right atrial pressure reading due to the LA-RA pressure equalizing capabilities of the pressure regulating device 400. Renal sodium and water retention are distinctive characteristics of heart disease that can be treated through the use of loop diuretics. However, loop diuretic administration may acutely increase cardiac afterload, left ventricular end-diastolic pressure, and worsen pulmonary edema in patients with heart failure. This response may be due to the effect of loop diuretics to stimulate renin-angiotensin-aldosterone system and sympathetic nervous system, both of which tend to reduce renal blood flow and increase resorption of sodium in the proximal and distal tubule. Further, loop diuretics may also cause excess urinary calcium losses, hyponatremia, ototoxicity, and the like. These complications may occur due to rapid infusion of high doses of the loop diuretic in patients.

Therefore, combining loop diuretic therapy with use of the pressure regulating device 400 may facilitate avoiding high doses of the loop diuretics (e.g. doses faster than 4 mg/min) by observing the right atrial pressure because the left atrial and right atrial pressure are substantially being equilibrated by the pressure regulating device 400.

The pressure regulating device 400 may also facilitate detecting oxygen saturation associated with the right atrial because blood flow between the RA and LA may increase as a result of implanting the pressure regulating device 400 between the LA and the RA. Also, an oxygen saturation sensor may be associated with the implanted pressure regulating device 400 to facilitate detection of blood oxygen levels on either side of an atrial wall. This may facilitate continuous oxygen measurement that might otherwise be a challenge with conventional superior vena cava (SVC) catheter-based measurements. Further, continuous measurement of the oxygen saturation with the help of the SVC catheter may be used to suggest medical therapies to a patient.

Combination Diagnostics/Sensing

The present disclosure may provide a means for sensing any of a variety of conditions associated with a subject using the disclosure. Certain parameters of the subject, such as those that may be directly sensed (blood pressure) and those that must be determined through analysis (example: a concentration of a medicine) may be monitored for the purpose of adjusting the control of the valve of the device 400. Sensing may be performed by a sensor and/or a combination of a sensor, a processor, and the like, such the device control facility 410 described herein. Device control facility 410 may be a representative embodiment of a processor-based device that may perform certain sensing functionality. Therefore, the following description references certain elements of the device control facility 410; however, other embodiments of the systems, methods, elements, and programs may be substituted herein.

One or more sensors 420 may send signals to the processor 412 which may be indicative of a parameter, or reading that the sensor 420 is capable of sensing. The processor 412 may use the sensor signal to produce an alert, notification, and the like and send it through the communication facility to an external monitor. The processor may process a plurality of sensor signals from one or more sensors to characterize a parameter over a period of time.

In embodiments, the device 400 may comprise a pressure monitor. The pressure monitor may be integrated with the pressure regulating device 400 or may be disposed separately from the pressure regulating device 400. The pressure monitor may be a pressure sensor. In a typical deployment of the device 400 the pressure monitor may measure right atrial pressure while the device 400 serves to lower the pressure of the left atrium. The pressure monitor may send a signal indicating a current pressure reading to the processor 412 and the processor 412 may send the pressure signal to an external monitor through the wireless communication facility 418. In embodiments, the pressure monitor may be used to capture a plurality of pressure measurements. The plurality of pressure measurements may be taken periodically with an inter-measurement time interval ranging from very short (near continuous measurements) to very long (occasional measurements). The pressure monitor may send each pressure measurement to the processor 412 as a separate signal or may send a continuous signal that varies based on the measured pressure. In an example, the pressure monitor may convert a measured pressure into a voltage that may be presented to the processor 412 over a communication medium, such as a wire. In embodiments, the processor 412 may use the communication facility 418 to send the pressure signal(s) to an external monitor.

In embodiments, the pressure monitor may measure pressure in both the right atrium and the left atrium. The pressure measurement taken may be used to make sure the device 400 is functioning. Based on an analysis of the expected pressure values and the measured pressure values, the processor 412 may determine if the pressure regulating device 400 is functioning properly. A plurality of pressure measurements by the pressure monitor may be used to monitor the efficacy of the device 400 and/or its control facility 410.

In embodiments, the device 400 may be used in combination with implantable devices for monitoring heart pressure in a patient to aid in the diagnosis, determination of the severity and management of cardiovascular diseases. In an example, the implantable device may be a pacemaker that may include a lead that may be inserted into the RA for measuring the pressure. The lead may include one or more sensors for measuring cardiac pressure on the right side of the heart. Because the pressure regulating device 400 is implanted to provide flow of blood between the left atrium and right atrium, pressure measured in the RA may be indicative of an LA pressure. The pressure variations representative of heart movement, i.e., contraction and relaxation, may be detected by the pressure sensor and may be transmitted to a proximal end of the lead. The transmitted information may be fed to the pacemaker. In embodiments, the pressure sensor may be able to transform such pressure signals into parameter signals for use in controlling a pacemaker operating variable such as pacing rate.

In embodiments, the device 400 may comprise a flow monitor. The flow monitor may measure the amount of blood flowing through the device 400. The flow monitor may use a sensor which is one of Doppler, ultrasound, and the like.

In embodiments, the device 400 may comprise an electric conductivity sensor. The electric conductivity sensor may measure the electric conductivity of a tissue within a heart or other organ. The electric conductivity sensor may be used to measure a heartbeat and may send a measurement to the processor 412 associated with the device 400. The processor 412 may send the measurement to an external monitor.

In yet another embodiment, the device 400 may comprise a chemistry sensor. The chemistry sensor may detect the presence of a chemical within one of a right atrium, a left atrium, a blood, and the like. The chemistry sensor may monitor a naturally occurring chemical, a chemical introduced through a therapy, and the like. Based on a signal provided by the chemistry sensor, the device control facility 410 may autonomously adjust a valve operating program to compensate for the detected chemistry, or may activate one of the components of the therapeutic facility described herein. In embodiments, the chemistry sensor may sense the amount of oxygen present in the blood. The chemistry sensor may send a signal indicative of the amount of oxygen present to a processor 412. The chemistry sensor may be used in combination with a therapeutic delivery system. For example, the indicative signal may be used to adjust the delivery of a medicine through the therapeutic delivery system in association with controlling the valve (e.g. with a device control facility 410) of the pressure regulating device 400. This may result in benefits to the patient of better regulation of an amount of medication being dispersed throughout the blood stream of the patient.

FIG. 66 depicts a block diagram illustrating various embodiments of the device 400. The device 400 may include one or more sensors 402 a-402 e that may detect a plurality of physiological parameters associated with the inside of the heart. For example, one or more sensors may observe and report a pulse, a pulse rate, pressure, flow, volume, temperature, blood-chemistry, electrical activities of tissues in contact with the sensor, and the like. Further, the device 400 may be in communication with a remote monitor facility 408 for observation and storage of data from sensors 402 a-402 e and from device 400. Remote monitor facility 408 optionally may include capabilities for displaying data from the sensors and controlling devices for delivering therapy to the patient.

Remote monitor facility 408 may be used to recommend appropriate treatment such as administration of drugs based on the physiological data obtained by the sensors. The appropriate treatment may be decided by the patient's attending physician or other medical professional, based on the data from the sensors and the patient's condition. The remote monitor facility 408 may be accessed by third party users such as doctors, nurses, Emergency Medical Technician (EMT), emergency monitoring vendors, and the like. The third party user may monitor transmitted parameters that are detected by the sensors. Accordingly, the third party user may provide instructions for administering drugs or other treatment to a patient 410 or the remote monitoring medical facility 408. The sensors, monitor facility 408, pressure regulating device 400, and the like may be monitored and/or controlled by a third party or by the patient 410.

In embodiments, a sensor such as the sensor 402 a may be secured on or integrally with the device 400. In another embodiment, a sensor such as the sensor 402 b may be implanted within the heart 412, but may be physically separate from the device 400. In yet another embodiment, a sensor such as the sensor 402 c may also be implanted in the body of the patient 410 outside the heart 412, such as to monitor blood sugar levels, and the like. In still another embodiment, a sensor such as sensor 402 d may be disposed on the body of the patient 410. For example, the sensor 402 d may be worn, for e.g. as a wristband, on the body of the patient 410 for monitoring pulse rate of the patient 410. In yet another embodiment, a sensor such as sensor 402 e may detect patient physical and physiological changes remotely. In the above-mentioned scenarios, the sensor or sensors 402 a-402 e may be connected either through a wireless communication or a wired communication with the device 400 and a remote monitor facility 408. The sensors 402 a-402 e may in general be hereafter referred to individually or jointly as a sensor 402.

In embodiments, the sensor 402 may be an acoustic sensor that may be implanted with the device 400. The acoustic sensor may be adapted to sense cardiac sounds in a heart 412 of the patient 410. Further, the acoustic sensor may convert a signal resulting from acoustic vibrations of the heart to an electrical signal. The electrical signals may be transmitted by the sensor 402 to a remote monitor and control facility 408. The monitor facility 408 may be configured to monitor and control the acoustic signals sent by the sensor 402. Further, the monitor facility 408 may display the acoustic signals that may be read by a third party such as a doctor, a nurse, and the like. Based on the displayed signals, a doctor may detect any heart-related complications, such as heart valve disorder, early stage of congestive heart failure, and the like, and may provide instructions to the monitor facility 408. In another embodiment, the sensor 402 may be secured to a pre-cordial patch (not shown) that may be worn by the patient 410. For example, the sensor 402 may be a phonocardiogram sensor for detecting the cardiac sound.

Further, the sensor 402 may be a chemical sensor that may be adapted to measure chemicals such as cardiac enzymes, brain natriuretic peptide (BNP), pH, creatinine, blood oxygen levels, and the like. The chemical sensor may also measure presence of biomarkers in the blood. For example, the chemical sensor may detect the presence of diagnostic biomarkers such as cardiac troponin for the diagnosis of myocardial infarction. The chemical sensor may also detect the presence of biomarkers related to different stages of diseases such as presence of BNP for congestive heart failure. The chemicals detected by the chemical sensor may be used by the device 400 to develop pacing, resynchronization, defibrillation or drug dispensing therapies. Further, information regarding the chemicals used for therapy or diagnostic purposes may be detected by the sensor 402 and may be provided to the data storage associated with the device 400 for later use by a physician, for instance, through the monitor facility 408.

In embodiments, the sensor 402 may be a pulse oximetry sensor that may detect oxygen saturation of the blood flowing through the heart 412 of the patient 410.

In embodiments, the sensor 402 may also be an electrocardiogram (ECG) sensor configured to detect cardiac electrical signals. In a scenario, if the sensor 402 detects irregular heartbeats, the sensor 402 may send such signals to the monitor facility 408. Healthcare providers may monitor the signals being displayed on the monitoring facility and then determine appropriate treatment, which according to some embodiments would be to send instructions to the monitoring facility 408. Appropriate care such as treatment or drugs would then be provided to the patient 410.

The sensor 402 may also be configured to produce electrical signals that may be representative of mechanical activity of the heart 412 of the patient 410. The mechanical activity of the heart 412 may enable healthcare providers to gather knowledge about the hemodynamic stability of the patient 410. Further, the sensor 402 may be integrated in an externally-applied sensor, which may be used to obtain or measure the heart rate of the patient 410. In embodiments, the sensor 402 may transmit infra-red light through the patient's skin, which may then be reflected back to the sensor 402. This may provide pulsatile flow of blood through capillaries, thereby producing accurate heart rate measurement. In an alternative embodiment, the sensor 402 may be connected through wires or fiber optic threads to the monitoring facility 408 for measuring the heart rate.

In embodiments, the sensor 402 may be a temperature sensor for detecting temperature of the blood entering and exiting the heart 412. In an example, the temperature sensor may include a thermistor that may be used to compensate temperature of the blood flow. Such temperature measurements may be useful for assessing cardiac efficiency. Further, changes in the temperature may be used for assessing cardiac pacing effectiveness.

In another embodiment, the sensor 402 may be a flow sensor that may be adapted to measure velocity and/or flow rate of a fluid such as blood in the heart 412. The flow sensor may measure the fluid velocity by sending and receiving pulses of ultrasound or light that may be reflected off blood cells and may experience Doppler shift.

Further, the sensor 402 may be capable of detecting blood pressure in the heart 412. In embodiments, the sensor 402 may include a pressure transducer (not shown) that may be adapted to measure pressure in a chamber such as a left atrial chamber or vessel such as a pulmonary artery. Further, the sensor may be worn on a wrist of the patient 410 to monitor and measure arterial pressure in the wrist.

As mentioned above, the sensor 402 may be disposed outside the body of the patient 410 such as the sensor 402 e. For example, the sensor 402 may come in contact with fluids while monitoring blood pressure of the patient 410. The sensor 402 may measure blood pressure when intravenous fluids (IV) may be administered to the patient 410. Further, the sensor 402 may send information about the blood pressure of the patient 410 to the remote monitor facility 408. The monitor facility 408 may be accessed by doctors who may take the necessary steps to treat the patient. For example, the doctors may contact the monitor facility 408 for information to decide whether to administer another drug to the patient 410. A doctor may also adjust dosage of the patient based on the signals received from the sensor 402.

FIG. 67 illustrates a drug administration facility 430 and a sensor 432 that may be implanted within the device 400. The drug administration facility 430 may communicate with a drug administration control 438. In embodiments, the drug administration facility 430 may communicate either through a wired mode or wirelessly with the drug administration control 438. In embodiments, the sensor 432 may be placed outside the device 400. The sensor 432 may detect any change in the physiological conditions of a patient. For example, the sensor 432 may be used to detect any change blood pressure, rate of muscle contraction, and the like. Based on the sensed conditions, the sensor 432 may generate signals. The signals generated by the sensor 432 may be transmitted to the drug administration control 438. The drug administration control 438 may analyze the signals and may send instructions to the drug administration facility 430 regarding the drugs that may be administered to the patient. The drug administration facility may also be known as a treatment facility, a therapeutic facility or a therapeutic administration facility. As such, the therapy administered may not be drugs, but rather could be electrical impulses, as from a pacemaker or other device for administering a therapy to the patient, especially a cardiac treatment administered to assist the heart of the patient.

In embodiments, the drug administration facility 430 may administer a desired dose of a therapeutic drug in accordance with the responsive signals sensed from the sensor 432. In another embodiment, the sensor 432 may detect the effect of the drugs that may be administered to the patient. Based on the detection by the sensor 432, the drug administration control 438 may facilitate the drug administration facility 430 to increase or decrease the dosage, administer a new drug, change the rate of administration of the dosage, and the like. In an exemplary embodiment, the drug administration control 438 may use the signal generated by the sensor 432 to produce an alert, a notification, and the like. For example, if the drug administration control 438 receives any signal from the sensor 432 that implies continuous change in the physiological conditions of the patient, the drug administration control 438 may sent alert signals to the drug administration facility 430 for immediately stopping the administration of the drug, and the like. Further, the drug administration control 438 may monitor various doses of a therapeutic drug that may be delivered to the patient's body based on the signal received from the sensor 432.

In another embodiment, one or more sensors 432 may be implanted in a patient's body in an area remote from the heart but in wireless contact with the drug administration facility 430 and its drug administration control unit 438. The sensor may detect one or more conditions that require treatment with a drug or medication available from the drug administration control unit. The drug administration unit may then dispense a quantity or a therapy over time of the needed drug or medication. Alternatively or in addition to administering the drug or medication, the drug administration control unit may signal an outside device or person of the need for treatment. The drug administration unit may be implanted in the patient, preferably in a location accessible from outside the patient. In one embodiment, the unit may be placed subcutaneously within the patient, in a location so that any reservoir of drug or medication may be conveniently replenished. For example, a liquid drug or medication may be replenished by a syringe re-filling a reservoir or supply of the drug within the drug administration unit 438.

Further, referring to FIG. 68, the device 400 may be used in combination with an implantable biomarker sensor 442 that may facilitate detection of targeted biomarkers associated with a heart condition. The implantable biomarker sensor 442 may contain antibodies that may target a specific biomarker and may allow the targeted biomarkers to be detected even if they are no longer in the bloodstream. The device 400, coupled with the biomarker sensor 442, may be placed in an atrial wall 407 of a patient's body. Further, the biomarker sensor 442 integrated with the pressure regulating device 400 may detect presence of biomarkers (enzymes or proteins) in flowing blood 409 from the left atrium to the right atrium. For example, cardiac enzymes such as creative phosphokinase, special sub-fractions of CPK, and troponin may be released into the blood by dying heart muscles and their levels may be measured in blood with the pressure regulating device 400. In another example, implanted biomarker sensors may contain antibodies targeting myoglobin, cardiac troponin I and creatinine kinase, for detection of a heart attack. See, for example, Implantable sensor detects whether heart attack has occurred, R&D Mag, MIT News (2 pages), Feb. 14, 2011, which is hereby incorporated by reference in its entirety. See also, Implantable Magnetic Relaxation Sensors Measure Cumulative Exposure to Cardiac Monitors, Yibo Ling et al., Nature Biotechnology 29 (273-277), Feb. 13, 2011, which is hereby incorporated by reference in its entirety. The biomarker sensor 442 implanted in the pressure regulating device 400 may enable early detection of heart disorders. In another embodiment, the biomarker sensor may be implanted in another area of the body remote from the device, such as under the dermis, where the sensor may be in contact with blood and accessible to an external device for reading the sensor and detecting the level of molecules bound to the sensor. In some embodiments, these sensors may be read with an external instrument, such as an MRI machine.

It should be appreciated that any of the above-described sensors could be placed within the barrel or cylindrical body of the flow control device (as shown in FIG. 67). Since blood will generally flow from LA to RA, this would be a favorable position for a sensor to sense may of the parameters mentioned above. Other embodiments may utilize sensors placed elsewhere on the body, such as near an external surface of the body.

Physiological Condition Sensing

The pressure regulating device 400 may be used in combination with acoustic or acceleration sensing to facilitate improved treatment and diagnosis of patients with heart conditions suitable for treatment with the pressure regulating device. To gain the benefit of such combination use, the device 400 may be associated with an accelerometer and/or acoustic sensor. The device may be coupled to or may comprise one or more accelerometer/acoustic sensors to facilitate comparing physical activity and heart rate or heart function. The accelerometer/acoustic sensor may be sensitive to and may respond to changes in posture, physical activity and body movements. In one example, the accelerometer/acoustic sensors may be used to monitor heart's motion with good resolution during a surgery. Such measurements, either during surgery or at other times may reveal patterns that may be an indicative of a change heart circulation failure due to the implanted pressure regulating device 400.

Assessment of need for treatment with a pressure regulating device 400 may be facilitated by a sensor/monitor that produces a plethysmography signal. In addition, post implantation benefit or change in pressure and/or volume may be detected through the use of such a sensor/monitor. Therefore, combination use of a plethysmography signal device and the pressure regulating device 400 may be indicated for improved treatment of patients. A plethysmography signal may be produced by an implantable sensor or a non-implanted sensor. Use of a plethysmography signal may facilitate improved treatment when combined with the pressure regulating device 400 because it may represent a cardiac cycle of a patient with an implanted pressure regulating device 400. The cardiac cycle may include a primary pulse, a secondary pulse, and a dicrotic notch. The dicrotic notch may separate the primary and secondary pulses. Further, signal analysis may facilitate determining the height of an area under the pulses which may change when a heart failure exacerbation is developed, thereby enabling heart performance assessment to be based at least in part on frequency characteristics of the plethysmography signal.

In embodiments, assessment of the heart failure status may be done based on morphology of the plethysmography signal representative of an arterial pulse pressure. The plethysmography signal may be indicative of changes in arterial blood volume. In an example, the plethysmography signal may be a photoplethysmography signal or an impedance plethysmography signal. Further, the implantable sensor may be an intra-arterial sensor, such as a pressure sensor, which may be implanted in an appropriate location, such as a pulmonary artery, so that a signal may be produced. In an exemplary embodiment, an implantable photoplethysmography (PPG) sensor may be used to obtain an arterial PPG waveform. The implant location of the pressure regulating device 400 may be suitable for facilitating sensing to produce the plethysmography signal and therefore integrating such a pressure monitor with the pressure regulating device 400 may be appropriate.

In another embodiment, if a non-implantable sensor is implemented, the plethysmography signal may be produced using a device that may easily clip on a finger, a toe, an earlobe or by employing a unique wearable sensor architecture that may estimate pulse wave velocity (PWV). The above mentioned technique may be used to calibrate peripheral pulse transit time measurements to arterial blood pressure. In this embodiment, a treatment plan that incorporates the pressure regulating device 400 may be combined with a non-implantable sensor to determine and/or provide feedback to control (manually or automatically) the pressure regulating device 400.

The pressure regulating device 400 may alternatively be used in combination with an intrathoracic impedance-based monitoring device to facilitate improved treatment and diagnosis of patients with heart conditions. Further, the intrathoracic impedance-based monitoring may facilitate the creation of an audible alert or notification for decompensating Congestive Heart Failure (CHF) in patients with the implantable device 400. Further, a monitoring device, such as the ones described herein, that may be used to monitor and/or control the pressure regulating device 400 may be adapted to work with the above-mentioned intrathoracic impedance-based monitoring device to create an alert.

Hemodynamic assessment may benefit from implanting the atrial pressure regulating device 400 in combination with a hemodynamic monitoring device that may further facilitate improved diagnosis and heart failure management by facilitating the flow of detectable diagnostic markers and therapeutic targets between the LA and RA.

The pressure regulating device 400 may be used in combination with a Piezo-electric sensor to facilitate improved monitoring and diagnosis of patients with heart conditions. The device 400 may be coupled to or may comprise one or more Piezo-electric sensors that may show low sensitivity to temperature and magnetic field fluctuations and high stability. The piezoelectric sensor may be used in a medical implantable lead that may be connected to a pace maker to monitor blood pressure and/or heart rate inside a heart. The piezo-electric sensor may also be used to measure the impact on an Arterial Pulse Wave Velocity (APWV) due to the implanted pressure regulating device 400.

The pressure regulating device 400 may be used in combination with an implantable biomarker detector that may facilitate detection of conditions associated with a heart attack and may help doctors to determine whether a patient has had a heart attack. The signs of an attack may usually remain in the bloodstream for days. The implantable biomarker detector, which may be a small implant, may contain iron oxide particles coated with antibodies that target a specific biomarker and may allow targeted biomarkers to be detected even if they are no longer in the bloodstream. The pressure regulating device 400 may be coupled with implantable biomarker detection capabilities to facilitate detection of targeted biomarkers that may be associated with a heart condition that could benefit from use of the implantable pressure regulating device 400.

The pressure regulating device 400 may be used in combination with an Implantable Loop Recorder (ILR) to facilitate improved monitoring and diagnosis of patients with heart conditions suitable for treatment with the pressure regulating device. The ILR may be used for atrial fibrillation monitoring. The ILR offers a powerful tool for investigation of syncope and undiagnosed arrhythmia. Further, the ILR may have the ability to record the electrical activity of the heart and store rhythm disturbances within set parameters. In a further embodiment, the monitoring capabilities of the ILR may be used for investigating the role of a right atrial linear ablation (RALA) procedure. The ILR may be coupled to the pressure regulating device 400 and may be implanted close to the subject's heart.

The pressure regulating device 400 may be used in combination with a device to monitor intracardiac impedance. The device may monitor cardiac electrophysiological parameters of a patient. The device may further monitor impedance in or near the atria of the heart. Further, the device may include an implantable impedance sensing circuit configured to sense an atrial impedance signal when coupled to a plurality of implantable electrodes and an impedance signal analyzer circuit. The impedance signal analyzer circuit may be configured to detect a sudden change in a characteristic of the sensed atrial impedance signal that indicates atrial tachyarrhythmia. The implant location of the pressure regulating device 400 may be suitable for monitoring the impedance in or near the atria of the heart and therefore, integrating such a device with the pressure regulating device 400 may be appropriate.

In addition to the various materials described herein and elsewhere that may be used in the pressure regulating device 400, nano-based technology may present opportunities for adding critical new capabilities to the device 400. Nano technology has enabled the production of nano sensors that may produce current during bending. Therefore, by combining such nano sensor technology with a pressure regulating device 400, it may be possible to have the device itself perform some sensing capabilities. Nano sensors may be implanted into the body to monitor changes in blood pressure. For example, the nano sensors may be implanted close to the right atrium for detecting any change in blood pressure. These sensors may bend due to the changes in the pressure, thereby creating a current and allowing blood pressure to be continuously measured. Further, the nano sensor may wirelessly transmit the pressure reading to an external receiver device. The external receiver device, which may display the data, may be worn on the wrist. In an exemplary embodiment, the nano sensors may be self-powered through combination with a nanogenerator. The nanogenerator may convert tiny movements of the human body (such as heart beats and blood flow) into electrical energy.

In embodiments, a treatment plan that includes the device 400 and Continuous Intra-Atrial Blood Gas Monitoring (CIABGM) for providing real time data concerning the state of a patient's blood oxygenation, gas exchange, and the like may provide benefits that either treatment alone cannot. The device 400 may be adapted to include an indwelling (in vivo) sensor (also known as intra-atrial sensors) to facilitate continuous blood gas monitoring without requiring a separate sensor residing in a peripheral artery. These sensors may measure the gases present in the peripheral arterial blood. Specifically, the CIABGM may be used for continuously measuring the PaO₂, PaCO₂, and arterial pH.

In embodiments, the pressure regulating device 400 may be adapted to provide defibrillation similar to a pacemaker. However, because the device 400 is implanted in the LA/RA wall, the defibrillation may operate similar to an atrial and ventricular defibrillating coil. The defibrillating coil may provide stimulation pulses on demand to a patient's heart whenever cardiac activity is not sensed, which may generate a shocking pulse to shock the patient's heart back into a normal rhythm whenever ventricular fibrillation may be sensed to be present. Accordingly, appropriate therapy, either in the form of stimulation pulses on demand or shocking pulses as required, may be provided to the patient.

In an exemplary embodiment, a heart monitor may be configured with the device 400. The heart monitor may sense atrial and ventricular fibrillation or other heart irregularities, and a defibrillating shock may be initiated in response by the device 400.

The pressure regulating device 400 may be used in combination with an implantable magnetic relaxation sensor that may facilitate diagnosis, evaluation, and monitoring of patients whose treatment includes the implanted pressure regulating device 400 and may be suspected of having other heart problems. The implantable magnetic relaxation sensor may be used to measure cumulative exposure to cardiac biomarkers. These cardiac biomarkers may be measured to help diagnose and monitor patients with suspected acute coronary syndrome (ACS). Further, the pressure regulating device 400 may be coupled with implantable magnetic relaxation sensor for identifying the presence of the biomarkers that indicate ACS as blood flows through the device 400. Cardio biomarkers may be detected in body fluids and may include detecting various proteins, molecular biology-bioreagents and the like. Cardio biosensors may support the study and treatment of human physiology because physiological fluids can affect biosensors such as those placed to detect flow through the pressure regulating device 400.

The pressure regulating device 400 may be adapted to facilitate monitoring cardiac pathologies in human beings. The adapted device 400 may include a monitoring capability that may be configured to detect and monitor heart irregularities such as inter-atrial block condition, atrial fibrillation, edema, and the like. One version of the adapted device 400 may measure a P wave electrical signal that may be generated from the atrium. The implant location of the pressure regulating device 400 (between the LA and RA) may be suitable for monitoring the P-wave signal. Alternatively, a P wave signal monitoring device may be disposed separately from the pressure regulating device 400 while communicating information related to the monitored heart irregularities and/or P wave signal data with the pressure regulating device.

The pressure regulating device 400 may be incorporated with a hermetically sealed pressure sensor module. Motion of a diaphragm of the pressure sensor module may be reflected as a change in the Right Ventricle (RV) pressure. Accordingly, the pressure sensor module may measure any changes in intracardiac impedance and may be helpful in adjusting the intracardiac pressure. In an example, the pressure sensor module may be hermetically implanted within any pacemaker. Further, the pressure sensor module may be hermetically sealed within either a right ventricular or right atrial lead. The pressure sensor module may be implanted with a pressure regulating device 400 thereby, gaining benefit from the use of the implantable pressure regulating device 400.

FIGS. 69 and 70 depict flowcharts for methods 470, 480 of using the sensors and other cardiac implantable electronic devices discussed above, along with a flow control device implanted in an atrial septum of a patient. FIG. 69 depicts a method 470 for administering a medication to a patient in response to the sensors and a command from a microprocessor mounted within the patient. In the first step 471 of the method, an opening is prepared in the atrial septum of the patient. If an opening already exists naturally, there may be no need to prepare the opening or it may be possible to simply enlarge the opening. Such techniques are discussed in co-pending U.S. patent application Ser. No. 13/370,913, filed Feb. 10, 2012, and entitled Apparatus and Method To Create and Maintain an Intra-atrial Pressure Relief Opening, now U.S. Pat. No. 8,882,697, which is hereby incorporated by reference in its entirety.

The next step 472 of the method is to mount a flow control device in the atrial septum of the patient. As seen above, in some embodiments the flow control portion of the device is simply remaining in place so that there is an opening to allow blood to flow from an area of higher blood pressure, typically in the patient's left atrium, to an area of lower pressure, typically in the patient's right atrium. In other embodiments, the flow control device may include one or more flow control elements, such as a flap, that are movable to allow more flow or less flow. In some instances, blood may also flow from the right atrium to the left atrium. In one embodiment, one or more sensors, as discussed above, may be mounted 473 within the patient and may be mounted on or near the flow control device implanted within the atrial septum. Thus, in some embodiments, this step may not be necessary, since a sensor or its output is already available for acquiring the necessary information. A reservoir or supply of medication, such as a liquid medication, may be mounted 474 within the patient fast delivery of a medication to the patient, particularly in response to an immediate need for medication to the patient. Examples include a diuretic, an antihypertensive, and an anticoagulant, which would furnish quick relief to the patient.

Once the appropriate elements are in place, e.g., implanted within the patient, the sensors and other devices may be used to monitor the health of the patient. For example, one or more of the sensors may sense 475 a heart condition of the patient, such as one or more pressures in regions of the heart, as a higher pressure in the left atrium and a lower pressure in the right atrium. An opening in the atrial wall normally would allow blood to flow from a region of higher pressure to a region of lower pressure, but there may be a blockage that prevents flow. Alternatively, the flow control device may use a flow control element, such as a flap, that may be controlled by one of the motors or actuators discussed above. In this instance, the pressure sensor will note the pressure differential and transmit 476 the signals or information to the microprocessor that receives the signals.

The microprocessor may be programmed as desired to take an action to alert the patient, to alert an external monitoring system or to administer 477 a medication to the patient from the implanted reservoir. For example, the patient may require a quantity of anticoagulant, which may be administered directly into the bloodstream or other appropriate medium of ingestion.

Another flow chart is depicted in FIG. 70, for a method 480 for adjusting a position of a flow control element of the flow control device. The steps of method 480 are similar to those of the other method discussed above. These steps include preparing an opening 481 in the atrial septum if needed, mounting 482 a flow control device in the patient's atrial wall, and mounting 483 at least one sensor within the patient. As noted above, in some embodiments, a sensor may already have been implanted or available to furnish the desired information, and thus step 483 may not be necessary. The sensors may then be used to sense 484 a heart condition of the patient, and the sensors will transmit 485 the information to the microprocessor. The microprocessor need not be mounted to the flow control device, but if the flow control element is to be manipulated, the microprocessor should be in communication with the flow control element in order to command the movement. For example, if the patient experiences a blood pressure differential in the atrial chambers, the microprocessor may be programmed to command an actuator or motor to move 486 a flap or other element in order to allow a freer flow of blood. Thus, in one embodiment the microprocessor may be implanted within the patient for closer communication with the flow control element and with the sensors, but may not be located within the patient's heart, while in other embodiments, the miniaturization may be easier if all components are co-located.

The discussion herein concerning sensing heart conditions has focused on the atrial septum and on blood flow from the left atrium to the right atrium, and to some extent, blood flow in the opposite direction, from the right atrium to the left atrium. A previous discussion concerned blood flow from the left atrium to the coronary sinus. Providing a passage from the left atrium to the coronary sinus is a technique that may also be used to relieve pressure in the left atrium. Accordingly, the techniques discussed with respect to FIGS. 63-70 may also be used with respect to FIGS. 53 to 62A-B. Thus, a sensing and control device may also be used to sense heart conditions near the coronary sinus and left atrium, just as sensing and control device 400 is used to sense conditions near the atrial septum.

The same types of sensors may be used near the coronary sinus to sense blood conditions, e.g., blood chemistry, and physical conditions, e.g., blood pressure, electrical characteristics and pulse rate. A flow control device may be used, as described in FIGS. 60-61 and their accompanying text, under the control of a microprocessor and a motor or actuator, as described in FIGS. 63-64 and their accompanying text. Placement of the microprocessor, a communications facility, or both, may be within the coronary sinus, near the heart, or within the patient. A system with these devices may also include a therapeutic facility within the patient for administering a therapy to the patient. The therapy may comprise administration of a drug, electrical pulses to portions of the heart, or other therapy as prescribed or directed by an attending physician or other medical professional caregiver. As also described above, the sensing and control device that is used near the coronary sinus may be used in a closed-loop control mode. In additional embodiments, the sensing and control device may be used in conjunction with an external monitoring station. The external monitoring station may receive information from the implanted sensor or sensors, a microprocessor in communication with the sensor or sensors, and communications facility. The external monitoring station may record all this information and make it available to the attending physician or other medical professional. The physician or other medical professional may then prescribe or direct a therapy to the patient, which may include a therapy possible with the implanted device or devices, or which may require intervention or a therapy from outside the patient.

The processors, facilities and controllers of the implantable devices, as well as the output devices, and monitoring devices, etc., deploy the subject Methods and System in full or in part, or in some cases a separately located machine may deploy the subject Methods and Systems in whole or in part. Thus, “machine” as referred to herein may be applied to the processors and controllers of the implantable devices, the output devices, and monitoring devices, etc. described above, a separate processor, separate interface electronics or combinations thereof.

The subject Methods and Systems disclosure may be implemented as a method on the machine, as a system or apparatus as part of or in relation to the machine, or as a computer program product embodied in a computer readable medium executing on one or more of the machines. In embodiments, the processor may be part of a server, client, network infrastructure, mobile computing platform, stationary computing platform, or other computing platform. A processor may be any kind of computational or processing device capable of executing program instructions, codes, binary instructions and the like. The processor may be or include a signal processor, digital processor, embedded processor, microprocessor or any variant such as a co-processor (math co-processor, graphic co-processor, communication co-processor and the like) and the like that may directly or indirectly facilitate execution of program code or program instructions stored thereon. In addition, the processor may enable execution of multiple programs, threads, and codes. The threads may be executed simultaneously to enhance the performance of the processor and to facilitate simultaneous operations of the application. By way of implementation, methods, program codes, program instructions and the like described herein may be implemented in one or more thread. The thread may spawn other threads that may have assigned priorities associated with them; the processor may execute these threads based on priority or any other order based on instructions provided in the program code. The processor, or any machine utilizing one, may include memory that stores methods, codes, instructions and programs as described herein and elsewhere. The processor may access a storage medium through an interface that may store methods, codes, and instructions as described herein and elsewhere. The storage medium associated with the processor for storing methods, programs, codes, program instructions or other type of instructions capable of being executed by the computing or processing device may include but may not be limited to one or more of a CD-ROM, DVD, memory, hard disk, flash drive, RAM, ROM, cache and the like. Nothing in this paragraph or the paragraphs below is meant to limit or contradict the description of the processing facility described herein and throughout.

A processor may include one or more cores that may enhance speed and performance of a multiprocessor. In embodiments, the process may be a dual core processor, quad core processors, other chip-level multiprocessor and the like that combine two or more independent cores (called a die).

The subject Methods and Systems described herein may be deployed in part or in whole through a machine that executes computer software on a server, client, firewall, gateway, hub, router, or other such computer and/or networking hardware. The software program may be associated with a server that may include a file server, print server, domain server, internet server, intranet server and other variants such as secondary server, host server, distributed server and the like. The server may include one or more of memories, processors, computer readable media, storage media, ports (physical and virtual), communication devices, and interfaces capable of accessing other servers, clients, machines, and devices through a wired or a wireless medium, and the like. The methods, programs or codes as described herein and elsewhere may be executed by the server. In addition, other devices required for execution of methods as described in this application may be considered as a part of the infrastructure associated with the server.

The server may provide an interface to other devices including, without limitation, clients, other servers, printers, database servers, print servers, file servers, communication servers, distributed servers and the like. Additionally, this coupling and/or connection may facilitate remote execution of program across the network. The networking of some or all of these devices may facilitate parallel processing of a program or method at one or more location without deviating from the scope of the disclosure. In addition, any of the devices attached to the server through an interface may include at least one storage medium capable of storing methods, programs, code and/or instructions. A central repository may provide program instructions to be executed on different devices. In this implementation, the remote repository may act as a storage medium for program code, instructions, and programs.

If the subject Methods and Systems are embodied in a software program, the software program may be associated with a client that may include a file client, print client, domain client, internet client, intranet client and other variants such as secondary client, host client, distributed client and the like. The client may include one or more of memories, processors, computer readable media, storage media, ports (physical and virtual), communication devices, and interfaces capable of accessing other clients, servers, machines, and devices through a wired or a wireless medium, and the like. The methods, programs or codes as described herein and elsewhere may be executed by the client. In addition, other devices required for execution of methods as described in this application may be considered as a part of the infrastructure associated with the client.

The client may provide an interface to other devices including, without limitation, servers, other clients, printers, database servers, print servers, file servers, communication servers, distributed servers and the like. Additionally, this coupling and/or connection may facilitate remote execution of program across the network. The networking of some or all of these devices may facilitate parallel processing of a program or method at one or more location without deviating from the scope of the disclosure. In addition, any of the devices attached to the client through an interface may include at least one storage medium capable of storing methods, programs, applications, code and/or instructions. A central repository may provide program instructions to be executed on different devices. In this implementation, the remote repository may act as a storage medium for program code, instructions, and programs.

The subject Methods and Systems described herein may be deployed in part or in whole through network infrastructures. The network infrastructure may include elements such as computing devices, servers, routers, hubs, firewalls, clients, personal computers, communication devices, routing devices and other active and passive devices, modules and/or components as known in the art. The computing and/or non-computing device(s) associated with the network infrastructure may include, apart from other components, a storage medium such as flash memory, buffer, stack, RAM, ROM and the like. The processes, methods, program codes, instructions described herein and elsewhere may be executed by one or more of the network infrastructural elements.

The methods, program codes, and instructions pertaining to the subject Methods and Systems described herein and elsewhere may be implemented on a cellular network having multiple cells. The cellular network may either be frequency division multiple access (FDMA) network or code division multiple access (CDMA) network. The cellular network may include mobile devices, cell sites, base stations, repeaters, antennas, towers, and the like. The cell network may be a GSM, GPRS, 3G, EVDO, mesh, or other networks types.

The methods, program codes, and instructions pertaining to the subject Methods and Systems described herein and elsewhere may be implemented on or through mobile devices. The mobile devices may include navigation devices, cell phones, mobile phones, mobile personal digital assistants, laptops, palmtops, netbooks, pagers, electronic books readers, music players and the like. These devices may include, apart from other components, a storage medium such as a flash memory, buffer, RAM, ROM and one or more computing devices. The computing devices associated with mobile devices may be enabled to execute program codes, methods, and instructions stored thereon. Alternatively, the mobile devices may be configured to execute instructions in collaboration with other devices. The mobile devices may communicate with base stations interfaced with servers and configured to execute program codes. The mobile devices may communicate on a peer to peer network, mesh network, or other communications network. The program code may be stored on the storage medium associated with the server and executed by a computing device embedded within the server. The base station may include a computing device and a storage medium. The storage device may store program codes and instructions executed by the computing devices associated with the base station.

The computer software, program codes, and/or instructions pertaining to the subject Methods and Systems may be stored and/or accessed on machine readable media that may include: computer components, devices, and recording media that retain digital data used for computing for some interval of time; semiconductor storage known as random access memory (RAM); mass storage typically for more permanent storage, such as optical discs, forms of magnetic storage like hard disks, tapes, drums, cards and other types; processor registers, cache memory, volatile memory, non-volatile memory; optical storage such as CD, DVD; removable media such as flash memory (e.g. USB sticks or keys), floppy disks, magnetic tape, paper tape, punch cards, standalone RAM disks, Zip drives, removable mass storage, off-line, and the like; other computer memory such as dynamic memory, static memory, read/write storage, mutable storage, read only, random access, sequential access, location addressable, file addressable, content addressable, network attached storage, storage area network, bar codes, magnetic ink, and the like.

The subject Methods and Systems described herein may transform physical and/or or intangible items from one state to another. The methods and systems described herein may also transform data representing physical and/or intangible items from one state to another.

The elements described and depicted herein and the functions thereof may be implemented on machines through computer executable media having a processor capable of executing program instructions stored thereon as a monolithic software structure, as standalone software modules, or as modules that employ external routines, code, services, and so forth, or any combination of these, and all such implementations may be within the scope of the present disclosure. Examples of such machines may include, but may not be limited to, personal digital assistants, laptops, personal computers, mobile phones, other handheld computing devices, medical equipment, wired or wireless communication devices, transducers, chips, calculators, satellites, tablet PCs, electronic books, gadgets, electronic devices, devices having artificial intelligence, computing devices, networking equipment, servers, routers and the like. Furthermore, the elements depicted in the flow chart and block diagrams or any other logical component may be implemented on a machine capable of executing program instructions. Thus, while the foregoing descriptions set forth functional aspects of the disclosed systems, no particular arrangement of software for implementing these functional aspects should be inferred from these descriptions unless explicitly stated or otherwise clear from the context. Similarly, it will be appreciated that the various steps identified and described above may be varied, and that the order of steps may be adapted to particular applications of the techniques disclosed herein. All such variations and modifications are intended to fall within the scope of this disclosure. As such, the depiction and/or description of an order for various steps should not be understood to require a particular order of execution for those steps, unless required by a particular application, or explicitly stated or otherwise clear from the context.

The subject Methods and Systems, and steps associated therewith, may be realized in hardware, software or any combination of hardware and software suitable for a particular application. The hardware may include a general purpose computer and/or dedicated computing device or specific computing device or particular aspect or component of a specific computing device. The processes may be realized in one or more microprocessors, microcontrollers, embedded microcontrollers, programmable digital signal processors or other programmable device, along with internal and/or external memory. The processes may also, or instead, be embodied in an application specific integrated circuit, a programmable gate array, programmable array logic, or any other device or combination of devices that may be configured to process electronic signals. It will further be appreciated that one or more of the processes may be realized as a computer executable code capable of being executed on a machine readable medium.

The computer executable code may be created using a structured programming language such as C, an object oriented programming language such as C++, or any other high-level or low-level programming language (including assembly languages, hardware description languages, and database programming languages and technologies) that may be stored, compiled or interpreted to run on one of the above devices, as well as heterogeneous combinations of processors, processor architectures, or combinations of different hardware and software, or any other machine capable of executing program instructions.

Thus, in one aspect, methods described above in connection with the subject Systems and Methods and combinations thereof may be embodied in computer executable code that, when executing on one or more computing devices, performs the steps thereof. In another aspect, the methods may be embodied in systems that perform the steps thereof, and may be distributed across devices in a number of ways, or all of the functionality may be integrated into a dedicated, standalone device or other hardware. In another aspect, the means for performing the steps associated with the processes described above may include any of the hardware and/or software described above. All such permutations and combinations are intended to fall within the scope of the present disclosure.

While the disclosure has been disclosed in connection with the preferred embodiments shown and described in detail, various modifications and improvements thereon will become readily apparent to those skilled in the art. Accordingly, the spirit and scope of the present disclosure is not to be limited by the foregoing examples, but is to be understood in the broadest sense allowable by law.

The use of the terms “a” and “an” and “the” and similar referents in the context of describing the disclosure (especially in the context of the following claims) is to be construed to cover both the singular and the plural, unless otherwise indicated herein or clearly contradicted by context. The terms “comprising,” “having,” “including,” and “containing” are to be construed as open-ended terms (i.e., meaning “including, but not limited to,”) unless otherwise noted. Recitation of ranges of values herein are merely intended to serve as a shorthand method of referring individually to each separate value falling within the range, unless otherwise indicated herein, and each separate value is incorporated into the specification as if it were individually recited herein. All methods described herein can be performed in any suitable order unless otherwise indicated herein or otherwise clearly contradicted by context. The use of any and all examples, or exemplary language (e.g., “such as”) provided herein, is intended merely to better illuminate the disclosure and does not pose a limitation on the scope of the disclosure unless otherwise claimed. No language in the specification should be construed as indicating any non-claimed element as essential to the practice of the disclosure.

While the foregoing written description enables one of ordinary skill to make and use what is considered presently to be the best mode thereof, those of ordinary skill will understand and appreciate the existence of variations, combinations, and equivalents of the specific embodiment, method, and examples herein. The disclosure should therefore not be limited by the above described embodiment, method, and examples, but by all embodiments and methods within the scope and spirit of the disclosure. 

What is claimed is:
 1. A system for treating a heart condition in a patient comprising: a body element comprising; a cylindrical core segment defining a passage; a first annular flange adapted to engage a first surface of an atrial septum of the patient; a second annular flange adapted to engage a second surface of the atrial septum of the patient; and a motor mounted to the body element includes a stationary portion and a movable portion, wherein the movable portion of the motor is anchored to a movable flap, wherein the movable flap is configured to move away from the stationary portion of the motor, forming an opening of the atrial septum, and allowing blood flow between left atrium and right atrium.
 2. The system of claim 1 further comprises a sensor that detects data related to at least one of blood chemistry, blood pressure, temperature, electrical characteristics of the patient's heart, chemical characteristics of the blood and biomarkers in the blood.
 3. The system of claim 2, further comprising a microprocessor in communication with the sensor.
 4. The system of claim 3, wherein the sensor is mounted within the patient remotely from the microprocessor and communicates wirelessly with the microprocessor.
 5. The system of claim 3 further comprising a wireless communications facility that receives and transmits data detected by the sensor and data generated by the microprocessor.
 6. The system of claim 5 wherein the wireless communication facility transmits the data from the sensors and the data generated by the microprocessor to an externally-located monitor.
 7. The system of claim 3 further comprising a therapeutic facility mounted within the patient, the therapeutic facility in communication with at least one of the microprocessor and sensor.
 8. The system of claim 7, wherein the therapeutic facility dispenses therapy based on at least one instruction received from the microprocessor and the data detected by the sensor.
 9. The system of claim 8 wherein the therapy comprises administration of a drug.
 10. The system of claim 3, wherein the microprocessor is mounted to or integral with at least one of said core segment, the first annular flange and the second annular flange.
 11. The system of claim 1, wherein the cylindrical core segment has a size of a first diameter when deployed, and wherein the cylindrical core segment is collapsible, enabling the cylindrical core segment to have a second diameter less than a size of the first diameter, thereby enabling percutaneous delivery of the system.
 12. The system of claim 1, wherein the second annular flange comprises a plurality of flange segments and wherein at least a portion of one of the flange segments of the second annular flange is more flexible or less flexible than another flange segment of the second annular flange.
 13. The system of claim 1, wherein the second annular flange comprises a plurality of flange segments, and wherein at least one of the flange segments of the second annular flange comprises a distal end adapted to be substantially parallel with and contact a septal wall when deployed, and wherein at least one end of the cylindrical core segment and the at least one of the flange segments of the second annular flange includes a first curved section that extends into an atrium so as to define a space between the at least one of the flange segments of the second annular flange and the septal wall when deployed and a second curved section that extends from the first curved section toward the septal wall and a distal end of at least one of the flange segments of the second annular flange.
 14. The system of claim 1, wherein each of the first and second annular flanges comprises a plurality of flange segments and wherein the first annular flange is adapted to engage a first surface of the atrial septum and wherein the second annular flange is adapted to engage a second surface of the atrium septum, and further comprising a third annular flange disposed between the first annular flange and the second annular flange along an axial length of the cylindrical core segment, the third annular flange comprising a plurality of flange segments having substantially similar lengths and less than lengths of the plurality of flange segments of the second annular flange, said plurality of flange segments of said third annular flange also adapted to engage said second surface of the atrial septum, wherein the first, second and third annular flanges are at least one of attached to and extending from the cylindrical core segment and wherein the cylindrical core is collapsible, enabling the cylindrical core segment to have a second diameter less than a first diameter of the cylindrical core segment when deployed, enabling percutaneous delivery of the system.
 15. The system of claim 1, wherein the second annular flange comprises a plurality of flange segments and wherein at least one flange segment of the plurality of flange segments of the second annular flange is longer than others of the plurality of flange segments of the second annular flange.
 16. A device for treating a heart condition in a patient comprising: a flow control device that comprises a stationary portion and a movable flap valve for mounting on an atrial septum of the patient; means for mounting the device on the atrial septum, wherein the means for mounting includes portions within the left atrium and portions within the right atrium of the patient; and a sensor mounted within the patient and in communication with the flow control device, wherein the movable flap valve is configured to move closer or away from the stationary portion of the flow control device based on information obtained by the sensor.
 17. The device of claim 16, further comprising a microprocessor in communication with the sensor.
 18. The device of claim 17, wherein the sensor is mounted within the patient in wireless communication with the microprocessor.
 19. The device of claim 16, wherein the sensor is adapted to be read by a device external to the patient.
 20. The device of claim 16, wherein the flow control device comprises a motor or actuator for moving a portion of the flow control device for controlling a flow of blood through the flow control device.
 21. The device of claim 16, further comprising a piezo actuator mounted to manipulate a portion of the flow control device for controlling a flow of blood through the atrial septum of the patient.
 22. The system of claim 3, wherein the microprocessor is configured to receive the information from the sensor and communicate the information to the valve element.
 23. The system of claim 1, wherein moving of the valve comprises partial opening of the valve.
 24. The system of claim 1, wherein moving of the valve comprises partial closing of the valve.
 25. The device of claim 23, wherein the microprocessor is configured to receive information from the sensor and communicate the information to the flow control device.
 26. The device of claim 1, further comprising a drug administering element adapted to administer a drug to the patient.
 27. The device of claim 16, further comprising a drug administering element adapted to administer a drug to the patient.
 28. The device of claim 2, wherein the sensor is mounted to any portion of the body element, including, for example, the first annular flange, the second annular flange, or the core segment. 